Polyphosphate-functionalized inorganic nanoparticles as hemostatic compositions and methods of use

ABSTRACT

A hemostatic composition is provided. The hemostatic composition includes a hemostatically effective amount of a hemostatic agent that includes a nanoparticle and a polyphosphate polymer attached to the nanoparticle. Also provided are medical devices and methods of use to promote blood clotting.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No.14/201,434, filed Mar. 7, 2014, now U.S. Pat. No. 9,186,417, whichclaims priority pursuant to 35 U.S.C. § 119(e) to the filing date ofU.S. Provisional Application No. 61/775,354, filed Mar. 8, 2013, thedisclosures of which are incorporated herein by reference.

GOVERNMENT SUPPORT

This invention was made with Government support under Grant No.W81XWH-11-2-0021 awarded by the Defense Advanced Research ProjectsAgency (DARPA) and Grant No. W911NF-10-2-0114 awarded by the ArmyResearch Office (ARO). The Government has certain rights in theinvention.

INTRODUCTION

Treatment of bleeding wounds, particularly severely bleeding wounds, canrequire immediate attention to bring the bleeding under control. Severebleeding poses a very real risk of death to the casualty if not treatedquickly. Although loss of about 10-15% of total blood volume can beendured without clinical sequelae in a healthy person, if a lacerationor penetrating trauma (e.g., knife or gun wound) is severe enough orinvolves critical arteries or veins, this volume of blood can be lost ina matter of minutes. The bleeding must be slowed immediately orirreversible damage to organs and mortality can result.

Bleeding wounds, even those that may be less severe, can pose seriousdifficulties and risks when a severe wound is inflicted in a remote areaor other situations (such as found in a battlefield) where full medicalassistance may be not immediately available. In such circumstances itcan be critical to undertake measures to slow or stop bleeding so thatthe subject can be transported to a medical facility.

Various methods and hemostatic compositions for promoting blood clottinghave been developed, and can be applied to help control bleeding in suchsituations. The field continues to develop additional hemostaticcompositions that provide for, for example, rapid initiation of bloodclotting, increased rate of blood clotting, sufficient blood clotstrength, and/or reduced adverse side effects. Of interest are suchhemostatic compositions that can be rapidly and safely applied in anemergency situation, such as on the battlefield or at the scene of anaccident, without the need for intensive training or equipment.

SUMMARY

A hemostatic composition is provided. The hemostatic compositionincludes a hemostatically effective amount of a hemostatic agent thatincludes a nanoparticle and a polyphosphate polymer attached to thenanoparticle. Also provided are medical devices and methods of use topromote blood clotting.

Aspects of the present disclosure include a hemostatic composition thatincludes a hemostatically effective amount of a hemostatic agent thatincludes a nanoparticle and a polyphosphate polymer attached to thenanoparticle.

In some embodiments, the polyphosphate polymer includes 20 or morephosphate monomers. In some embodiments, the polyphosphate polymerincludes 70 or more phosphate monomers.

In some embodiments, the hemostatic agent has a polyphosphate polymer tonanoparticle mass ratio of 1:2 or more. In some embodiments, thehemostatic agent has a polyphosphate polymer to nanoparticle mass ratioof 1:1 or more.

In some embodiments, the nanoparticle includes a material such assilica, diatomaceous earth, titanium dioxide, and calciumhydroxyapatite. In some embodiments, the nanoparticle includes silica.

In some embodiments, the nanoparticle has an average diameter of 100 nmor less.

In some embodiments, the hemostatic agent further includes a protectingagent attached to the hemostatic agent by an enzymatically-cleavablelinking group. In some embodiments, the protecting agent includes apolyethylene glycol polymer. In some embodiments, the polyethyleneglycol polymer has a molecular mass of 1000 Da or more.

Aspects of the present disclosure include a medical device that includesa hemostatic composition and a sterile substrate on which the hemostaticcomposition is disposed. The hemostatic composition includes ananoparticle and a polyphosphate polymer attached to the nanoparticle.

In some embodiments, the substrate is adapted for delivery of thehemostatic composition to a bleeding wound. In some embodiments, thesubstrate is a bandage, gauze, or sponge.

In some embodiments, the medical device includes a sealed packagecontaining the hemostatic composition.

Aspects of the present disclosure include a method of promoting bloodclotting at a hemorrhage site. The method includes administering to ahemorrhage site in a subject the hemostatic composition as describedherein for a period of time sufficient to at least initiate bloodclotting at the hemorrhage site.

In some embodiments, the hemorrhage site is an external hemorrhage site.In some embodiments, the administering includes applying the hemostaticcomposition to the external hemorrhage site.

In some embodiments, the hemorrhage site is an internal hemorrhage site,and the hemostatic composition is a hemostatic composition includes aprotecting agent attached to the hemostatic agent by anenzymatically-cleavable linking group. In some embodiments, theadministering includes intravenously administering the hemostaticcomposition to the subject.

These and other embodiments of the invention will be readily apparent tothe ordinarily skilled artisan upon reading the present specification.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a graph of average particle size (nm) vs. amount of NH₄OH(%) added to a reaction to produce silica nanoparticles, according toembodiments of the present disclosure.

FIG. 2 shows a graph of the yield (%) vs. amount of NH₄OH (%) added to areaction to produce silica nanoparticles, according to embodiments ofthe present disclosure.

FIG. 3 shows a graph of R value (min) vs. concentration (mg/mL) ofsilica nanoparticles (SNP) and silica nanoparticles functionalized withpolyphosphate polymer (SNP-P70) (70 monomer chain length) at 37° C. and10.8 mM Ca²⁺, according to embodiments of the present disclosure.

FIG. 4 shows TEM micrographs of silica nanoparticles of 55 nm averagesize, according to embodiments of the present disclosure.

FIG. 5 shows a graph of clotting time, R, for SNP-P70 and lipidatedtissue factor (LTF) at various dilutions of pooled normal plasma (PNP)at 37° C. and 10.8 mM Ca²⁺, according to embodiments of the presentdisclosure.

FIG. 6 shows a graph of clotting time (R) for various conditions usingFXII deficient plasma, according to embodiments of the presentdisclosure. SNP-P70 showed the smallest and most consistent R value. Thelast bar in the graph was a control using lipidated tissue factor (LTF)in pooled normal plasma (PNP).

FIG. 7 shows a graph of coagulation index (CI) for various conditionsusing FXII deficient plasma (higher index indicates increased clotting),according to embodiments of the present disclosure. SNP-P70 had thehighest and most consistent CI value. The last bar in the graph was acontrol using lipidated tissue factor (LTF) in pooled normal plasma(PNP).

FIG. 8 shows a graph of clotting time, R, for various differentpolyphosphate (P700) to SNP ratios (0.2, 0.4, 0.6, and 1), according toembodiments of the present disclosure.

FIG. 9 shows fluorescence microscope images of a thrombin-specific bluecoumarin dye experiment to qualitatively determine the coagulationthreshold response, according to embodiments of the present disclosure.FIG. 9 (left) shows an image of the blue coumarin dye experiment at time0 min, and FIG. 9 (right) shows an image of the blue coumarin dyeexperiment at time 20 min.

FIGS. 10A and 10B show a graph of fluorescence intensity (a.u.) vs. timefor various concentrations of SNP and SNP-P70 (see FIG. 10A), and agraph of clot time (half-time, s) vs. concentration (mg/mL) for SNP andSNP-P70 (see FIG. 10B), according to embodiments of the presentdisclosure.

FIG. 11A shows a graph of clotting time, R, (min) vs. % of pooled normalplasma (PNP) for experiments to determine hemostatic activity in dilutedsamples, according to embodiments of the present disclosure. FIG. 11Bshows a graph of clot size, MA, (mm) vs. % of pooled normal plasma(PNP), according to embodiments of the present disclosure.

FIG. 12A shows a graph of fluorescence vs. time (sec) for thrombingeneration times from 100% plasma to 25% plasma (i.e., 100% plasma is100% plasma and 0% dilutant) with no SNP-P70 added. FIG. 12B shows agraph of fluorescence vs. time (sec) for thrombin generation times atvarious dilution conditions for samples with SNP-P70 added, according toembodiments of the present disclosure.

FIG. 13A shows a graph of clotting time, R, (min) vs. temperature (° C.)for experiments to determine hemostatic activity of SNP-P70 underhypothermic conditions, according to embodiments of the presentdisclosure. FIG. 13B shows a graph of coagulation index (CI) vs.temperature (° C.) for SNP-P70 under hypothermic conditions, accordingto embodiments of the present disclosure.

FIG. 14 shows a schematic of a silica nanoparticle that includes PEGattached to the nanoparticle through a cleavable peptide linking groupthat may be cleaved by Factor Xa, thrombin or other enzymes, accordingto embodiments of the present disclosure.

FIG. 15 shows a graph of clotting time, R, vs. 3-aminopropyltriethoxysilane (APTES) to SNP ratio, according to embodiments of thepresent disclosure.

FIG. 16 shows a graph of clotting time, R, for unfunctionalized SNP andvarious functionalized SNPs (Pep: peptide; SPDP: succinimidyl3-(2-pyridyldithio)propionate; PEG used was 2 kDa), according toembodiments of the present disclosure.

FIG. 17 shows graphs of the size-dependence of a phosphate polymer's(polyP's) procoagulant activities, according to embodiments of thepresent disclosure. Data are plotted as % maximal activities versusphosphate polymer (polyp) polymer length.

FIG. 18 shows a graph of the efficiency of dendrimer-polyP conjugationat different pH, temperature and time conditions, according toembodiments of the present disclosure.

FIG. 19 shows a graph of the stability of polyP at 37° C. and various pHconditions, according to embodiments of the present disclosure.

FIG. 20 shows a graph of dendrimer running through the Econo-Pac 10 DGColumns, according to embodiments of the present disclosure. The runningphase was DI water.

FIG. 21 shows a graph of dendrimer running through the Econo-Pac 10 DGColumns, according to embodiments of the present disclosure. The runningphase was 25 mM borate acid buffer at pH 9.

FIG. 22 shows a graph of dendrimer-polyP running through the Econo-Pac10 DG Columns, according to embodiments of the present disclosure. Therunning phase was borate acid buffer. The reading was for dendrimer.

FIG. 23 shows a graph of dendrimer-polyP running through the Econo-Pac10 DG Columns, according to embodiments of the present disclosure. Therunning phase was borate acid buffer. The running phase was borate acidbuffer. The reading was for polyP.

FIG. 24 shows a graph of dendrimer-polyP running through the BG P-10 Gelpacked columns, according to embodiments of the present disclosure. Therunning phase was 1M LiCl. The reading was for dendrimer.

FIG. 25 shows a graph of dendrimer-polyP running through the BG P-10 Gelpacked columns, according to embodiments of the present disclosure. Therunning phase was 1M LiCl. The reading was for PolyP.

FIG. 26 shows a graph of PolyP concentration before and after glass milkassay performed on two previous reactions, according to embodiments ofthe present disclosure.

FIG. 27 shows a graph of the concentration of primary amine and PolyPbefore and after glass milk separation assay, according to embodimentsof the present disclosure.

FIG. 28 shows a graph of a blood clotting test for Dendrimer-PolyPconjugation, according to embodiments of the present disclosure.

FIG. 29 shows a graph of PS-polyP conjugation, according to embodimentsof the present disclosure. The reaction conditions were at roomtemperature, pH4, and 24 hours.

FIG. 30 shows a graph of the amount of amine exposed on the surface ofthe PS particles at pH 4, according to embodiments of the presentdisclosure.

FIG. 31 shows a graph of 24 and 48 hour primary amine concentration of aligand polyP reaction vs. control under conditions without EDAC,according to embodiments of the present disclosure.

FIG. 32 shows a calibration curve of primary amine concentration atexcitation and emission wavelengths of 410 and 480 nm, respectively,according to embodiments of the present disclosure.

FIG. 33 shows a graph of primary amine concentration after theamine-thiol ligand reacted with polyP, according to embodiments of thepresent disclosure.

FIG. 34, panel A, shows the gold nanoparticles ligand mixture beforecentrifugation, according to embodiments of the present disclosure. FIG.34, panel B, shows gold particle pellet after centrifugation, accordingto embodiments of the present disclosure.

FIG. 35, panel A, and FIG. 35, panel B, show a schematic of thePLGA-based silica nanoparticle synthesis, according to embodiments ofthe present disclosure. As shown in FIG. 35, panel A, samples areinserted into the dispersing channel. The inlet channel contains sol-gelsilica, which precipitates upon contact with the media to form sphericalnanoparticles. FIG. 35, panel B, shows a side view of the schematic,which illustrates how the spherical nanoparticles form. Particle sizesfor PLGA averaged about 125 nm.

FIG. 36 shows a graph of zeta potentials of FMSnf, FMS-nf loaded withpolyP, and FMS-nf loaded with APTES particles, according to embodimentsof the present disclosure.

FIG. 37 shows scanning electron microscopy (SEM) images of silicananoparticles (NPs), e.g., mesocellular foam, prepared using the PLGAsystem, according to embodiments of the present disclosure. Averageparticle diameter was 125+/−25 nm as determined by dynamic lightscattering. The conjoined nature of the separate particles occurred dueto sputtering for SEM imaging.

FIG. 38 shows a graph of pore size distribution of mesocellular foamscalculated desorption branch by BJH method, according to embodiments ofthe present disclosure.

FIG. 39 shows a graph of pore size distribution of porous silicacalculated desorption branch by BJH method, according to embodiments ofthe present disclosure.

FIG. 40 shows SEM images of TiO₂ synthesized via the phosphoric acidpathway, according to embodiments of the present disclosure. Theconjoined nature of the separate particles occurred due to sputteringfor SEM imaging.

FIG. 41 shows a FT-IR spectrum of unmodified and APTES-modified titaniananoparticles, according to embodiments of the present disclosure. C—H,N—H, and Si—O—Si bands indicated successful attachment of APTES to TiO₂molecules.

FIG. 42 shows a graph of zeta potential titration of unmodified andmodified titania nanoparticles, according to embodiments of the presentdisclosure.

FIG. 43, left, shows images of the uptake of various samples by HUVEC(Human Umbilical Vein Endothelial Cells), with Ag NP concentration of 10μg/ml; Kaolin concentration of 10 μg/ml; and MCF-26 concentration of 100μg/ml. FIG. 43, right, shows images of the uptake of various samples byHDFs, with Ag NP concentration of 20 μg/ml; Kaolin concentration of 20μg/ml; and MCF-26 concentration of 100 μg/ml.

FIG. 44 shows a mechanism for attaching thrombin to solid silica using aprotein cross-linker, according to embodiments of the presentdisclosure.

FIG. 45 shows a process work flow and image of a thiol sensingcolorimetric assay to verify hydroxylamine deprotection of solid silicananoparticles, according to embodiments of the present disclosure.

FIG. 46 shows a graph of clotting time (R, min) versus particle size(nm) of silica nanoparticles at a concentration of 0.68 mg/mL, accordingto embodiments of the present disclosure. Experimental conditions: 37°C., 22 mM Ca²⁺.

FIG. 47 shows a graph of clotting time (R, min) versus finalconcentration (mg/mL) of silica nanoparticles of 55 nm size in the TEG,according to embodiments of the present disclosure. 0.68 to 1.35 mg/mLwas deemed optimal, with the threshold being ˜0.5 mg/mL. Experimentalconditions: 37° C., 11 mM Ca²⁺.

FIG. 48 shows a graph of particle size and polydispersity index (PDI)versus concentration of the silica nanoparticles, according toembodiments of the present disclosure. The particles were stable acrossthe range of experimental concentrations. Experimental conditions: 20°C., pH 6.8.

FIG. 49 shows a graph of clotting time (R, min) versus the concentrationof silica nanoparticles with and without polyphosphate, according toembodiments of the present disclosure. Experimental conditions: 37° C.,weight ratio SiO₂:P-70=1:1, 116 nm, 11 mM Ca²⁺.

FIG. 50 shows a graph of the relationship between zeta potential and pHfor silica particles ones coated with APTES, according to embodiments ofthe present disclosure. Experimental conditions: 20° C., 12.5 mg/mL, 112nm diameter, batch was low-amine coated particles.

FIG. 51 shows a graph of clotting time (R, min) of the silica particlescoated with APTES, with and without amine PEGylation, according toembodiments of the present disclosure. Delta R was optimal at the lowamine density. Experimental conditions: 37° C., 1.35 mg/mL, 112 nm.

FIG. 52 shows a graph of the effects of polyP45-Au nanoparticles (10 nm)on Factor Xa-mediated clotting time, according to embodiments of thepresent disclosure. The phosphate concentration was kept at 9.8 μm.

FIG. 53 shows a graph of clot time versus polyphosphate concentration,according to embodiments of the present disclosure. Nanoparticleconcentration was 12.9 nM.

FIG. 54 shows TEM micrographs of SNP of ˜55 nm size, according toembodiments of the present disclosure.

FIG. 55 shows a graph of particle size of SNP based on % NH₄OH added,according to embodiments of the present disclosure.

FIG. 56 shows a graph of silica yield based on % NH₄OH added, accordingto embodiments of the present disclosure.

FIG. 57 shows TEM micrographs of Ag@SNP and a schematic of the particle:silver (Ag) core and silica (SiO₂) shell, according to embodiments ofthe present disclosure.

FIG. 58 shows a graph of clotting time (R, min) versus stockconcentration (mg/mL) of the silica nanoparticles of different sizes,according to embodiments of the present disclosure. 50 mg/mL correspondsto 1.35 mg/mL in TEG cup. Experimental conditions: 37° C., 11 mM Ca²⁺.

FIG. 59A shows a graph of clotting time of SNP with and withoutpolyphosphate (P70) as a function of concentration; and FIG. 59B shows agraph of clotting time of different samples, including SNP, SNP-P70 andKaolin, according to embodiments of the present disclosure.

FIG. 60 shows a graph of clotting time (R) for various conditions usingFXII deficient plasma, according to embodiments of the presentdisclosure. SiO₂-P70 had the smallest and most consistent R value. Lastbar was a control using pooled normal plasma.

FIG. 61 shows a graph of coagulation Index (CI) for various conditionsusing FXII deficient plasma, according to embodiments of the presentdisclosure. SiO₂-P70 had the highest and most consistent CI value. Lastbar was a control using pooled normal plasma.

FIG. 62 shows a graph of clotting time (R) vs. APTES/SNP (μL/g) forAPTES, 5 k PEG and 20 k PEG SNPs, according to embodiments of thepresent disclosure.

FIG. 63 shows a schematic of FXa (found in the wound site) thatrecognizes peptide sequence (IEGR) and cleaves PEG off the TSP toselectively activate coagulation, according to embodiments of thepresent disclosure.

FIG. 64 shows a graph of clotting times of functionalized silicaparticles, according to embodiments of the present disclosure. (Pep:peptide, PEG used is 2 k).

FIG. 65 shows a graph of clotting time (R) of various anatase titaniasynthesis at different stock concentrations, according to embodiments ofthe present disclosure. Experimental conditions: 37° C., 11 mM Ca²⁺.

FIG. 66 shows a graph of clotting times of TNP with and withoutpolyphosphate (P70) at a concentration of 100 mg/mL (stock), accordingto embodiments of the present disclosure.

FIG. 67 shows a graph of clotting times for PEGylated TNP, according toembodiments of the present disclosure.

FIG. 68 shows a graph of the pH dependent hydrolysis of P-N bond ofpolyP-cystamine conjugate, according to embodiments of the presentdisclosure.

FIG. 69 shows graphs of the clotting data for the gold particlespresented in Table 8 when assayed for the ability to activate thecontact pathway, according to embodiments of the present disclosure.

FIG. 70 shows images of: (Left) Blue coumarin dye experiment at time 0min; and (Right) Blue coumarin experiment at time 20 min, according toembodiments of the present disclosure.

FIG. 71 shows an image of polyacrylamide gel electrophoresis (PAGE) ofmaterial acquired during time course of hydrolysis with unbuffered LiCl,according to embodiments of the present disclosure.

FIG. 72 shows an image of PAGE material acquired during time course ofhydrolysis with alkaline LiCl, according to embodiments of the presentdisclosure.

FIG. 73 shows an image of PAGE of size fractionated high yield polyP,according to embodiments of the present disclosure.

FIGS. 74A-74C show graphs of size distribution of gold nanoparticlesmeasured by DLS, according to embodiments of the present disclosure.Molar ratio of citrate to gold was (FIG. 74A) 4:1, (FIG. 74B) 3:1 and(FIG. 74C) 1:1.

FIG. 75, panel A, and FIG. 75, panel B, show schematics of the processof synthesizing gold nanoparticles conjugated with polyP, according toembodiments of the present disclosure. FIG. 75, panel A, shows polyPconjugated to cystamine, and FIG. 75, panel B, shows polyP-cystamineattached to the surface of gold nanoparticles.

FIG. 76 shows a schematic of the determination of the minimum andmaximum radius based on the geometry of a centrifuge, according toembodiments of the present disclosure.

FIG. 77 shows a graph of cumulative clotting activity for 10 nm, 15 nm,and 50 nm polyP45-gold nanoparticles (refer to Table 13 for sampleinformation), according to embodiments of the present disclosure.

FIG. 78 shows a graph of cumulative clotting activity for 10 nm, 15 nm,and 50 nm polyP70-gold nanoparticles (refer to Tables 14 and 15 forsample information), according to embodiments of the present disclosure.

FIG. 79 shows a graph of contact pathway activation of polyP70-50 nmgold nanoparticles (refer to Table 14 for sample information) at aconstant gold particle concentration, according to embodiments of thepresent disclosure.

FIG. 80 shows contact pathway activation data for polyP70-50 nm goldnanoparticles (refer to Table 14 for sample information) at constantphosphate concentration, according to embodiments of the presentdisclosure.

FIG. 81 shows contact pathway activation data for polyP70-Peg (3:1)-50nm gold nanoparticles (refer to Table 15 for sample information) atconstant gold nanoparticle concentration, according to embodiments ofthe present disclosure.

FIG. 82 shows a graph of fluorescent measurements for induction of thecontact pathway with aqueous polyP45 using a fluorogenic thrombinsubstrate, according to embodiments of the present disclosure.

FIG. 83, panel A, to FIG. 83, panel D, show the assembly and disassemblyof inter-molecular hydrogen bonding between PAAc and PAAm, according toembodiments of the present disclosure. FIG. 83, panel A, shows aschematic representation. FIG. 83, panel B, shows an image of PAAc andPAAm aqueous solutions were mixed thoroughly at 20° C. FIG. 83, panel C,shows an image of a mixture that was heated to 40° C. FIG. 83, panel D,shows an image of a solution that was cooled back to 20° C.

FIG. 84, panel A, and FIG. 84, panel B, show schematics of the processof synthesizing gold nanoparticles conjugated with the thermosensitivepolymers, according to embodiments of the present disclosure. FIG. 84,panel A, shows a reaction for the conjugation of PAAc or PAAm tocystamine or DDA. FIG. 84, panel B, shows PAAc-cystamine or PAAm-DDAattached to the surface of gold nanoparticles.

FIG. 85 shows a graph of the size distribution of the nanoparticlesafter mixing PAAc_10nm_polyP(13) with PAAm_10nm_polyP(13) at a 1:1 ratioat 25° C., 33° C. and 37° C., according to embodiments of the presentdisclosure.

FIG. 86 shows a graph of the size distribution of the nanoparticlesafter mixing PAAc_10nm_polyP(11) with PAAm_10nm_polyP(11) at a 1:1 ratioat 25° C. and 37° C., according to embodiments of the presentdisclosure.

FIG. 87 shows a graph of particle size of SNP based on % NH₄OH added,according to embodiments of the present disclosure.

FIG. 88 shows a graph of silica yield based on % NH₄OH added, accordingto embodiments of the present disclosure.

FIG. 89 shows a graph of clotting time for SNP-P70, which had a shorterclotting time (R, min) at half the concentration than bare silica,according to embodiments of the present disclosure. Experimentalconditions: 37° C., 11 mM Ca²⁺.

FIG. 90 shows a graph of clot time for various ratios of P700:SNP (0.2,0.4, 0.6, and 1), according to embodiments of the present disclosure.

FIG. 91 shows a graph of fluorescence intensity over time, which showsthat SNP-P70 generated thrombin quicker than SNP, according toembodiments of the present disclosure.

FIG. 92 shows a graph of the same fluorescence data as in FIG. 91,presented in terms of clot time.

FIG. 93 shows a graph of thrombin generation times from 100% plasma to25% plasma; i.e.: 100% is 100% plasma and 0% dilutant, according toembodiments of the present disclosure.

FIG. 94 shows a graph of fluorescence over time, which indicated thatadding SNP-P70 generated thrombin quickly even under severe plasmadilution, according to embodiments of the present disclosure.

FIG. 95 shows a graph of clot time vs. temperature, which indicated thatSNP-P70 TSPs initiated clots quicker under hypothermia, according toembodiments of the present disclosure.

FIG. 96 shows a graph of Coagulation index (CI) vs. temperature, whichindicated that SNP-P70 improved clot formation compared to lipidatedtissue factor (LTF), according to embodiments of the present disclosure.

FIG. 97 shows a graph of clotting times for various SNPs, according toembodiments of the present disclosure.

FIG. 98 shows a graph of the relationship between zeta potential andclotting time for SNP with and without APTES, according to embodimentsof the present disclosure.

FIG. 99 shows a graph of zeta potential vs. the ratio of APTES/TEOS usedin the synthesis of SNPs, according to embodiments of the presentdisclosure.

FIG. 100 shows a graph of zeta potential vs. the ratio of APTES/TEOS forcalcined and not calcined SNPs, according to embodiments of the presentdisclosure.

FIG. 101 shows a graph of clotting time vs. zeta potential for calcinedand not calcined SNPs, according to embodiments of the presentdisclosure.

FIG. 102 shows Table 8, which shows the sample conditions for polyP70conjugated to gold nanoparticles (10 nm, 15 nm, and 50 nm), according toembodiments of the present disclosure.

DEFINITIONS

A “hemostatic agent” refers to an agent which promotes blood clotting,e.g., following administration to hemorrhage site (e.g., an external orinternal wound). Hemostatic agents encompass, for example, inorganicmaterials (e.g., silica nanoparticles, polyphosphate, and the like, asdescribed herein), as well as biologically active ions (e.g., ions thatact as cofactors in the clotting cascade (e.g., by serving as an ionicbridge)), and/or facilitated colloid precipitation (e.g., red blood cellprecipitation), clotting factor proteins (e.g., thrombin, etc.),combinations thereof, and the like.

A “hemostatic composition” refers to a composition that includes atleast one hemostatic agent. A hemostatic composition may further includeone or more additional components, which may be hemostatically active(e.g., promote blood clotting or promote activity of the hemostaticagent in the hemostatic composition in blood clotting). Hemostaticcompositions can also contain agents that are hemostatically inert.

The term “hemostasis” as used herein refers to inhibition of bleeding,including the arrest of bleeding, which is accompanied by blood clotformation.

A “hemostatically effective amount” refers to an amount of a hemostaticcomposition which, following application to a hemorrhage site, iseffective to facilitate blood clotting (e.g., as compared to time toclot formation in the absence of the hemostatic agent), increase bloodclotting rate as compared to a blood clotting rate in the absence of thehemostatic agent, and/or improve blood clot strength as compared toblood clot strength in the absence of the hemostatic agent. Clotstrength can be measured by Thrombelastograph® (TEG) measurements.Assays for assessing hemostatic activity are known in the art, withexemplary methods described herein.

The term “isolated” means the compound is present in an environmentother than that in which it is found in nature. “Isolated” is meant toinclude compounds that are within samples that are substantiallyenriched for the compound of interest and/or in which the compound ofinterest is partially or substantially purified.

As used herein, the term “purified” refers to a compound that is removedfrom its natural environment and is at least 60% free, such as 75% ormore free, or 90% or more free from other components with which it isnaturally associated.

The terms “individual,” “subject,” “host,” and “patient,” usedinterchangeably herein, refer to any subject in need to treatment, e.g.,mammals, including, but not limited to, humans, simians, felines,canines, equines, bovines, mammalian farm animals, mammalian sportanimals, and mammalian pets. Human subjects in need of treatment are ofinterest.

The terms “polypeptide,” “peptide,” and “protein” are usedinterchangeably herein to refer to a polymeric form of amino acids ofany length. Unless specifically indicated otherwise, “polypeptide,”“peptide,” and “protein” can include genetically coded and non-codedamino acids, chemically or biochemically modified or derivatized aminoacids, and polypeptides having modified peptide backbones. The termincludes fusion proteins, including, but not limited to, fusion proteinswith a heterologous amino acid sequence, fusions with heterologous andhomologous leader sequences, proteins which contain at least oneN-terminal methionine residue (e.g., to facilitate production in arecombinant bacterial host cell); immunologically tagged proteins; andthe like.

Before the present invention is further described, it is to beunderstood that this invention is not limited to particular embodimentsdescribed, as such may, of course, vary. It is also to be understoodthat the terminology used herein is for the purpose of describingparticular embodiments only, and is not intended to be limiting, sincethe scope of the present invention will be limited only by the appendedclaims.

Where a range of values is provided, it is understood that eachintervening value, to the tenth of the unit of the lower limit unlessthe context clearly dictates otherwise, between the upper and lowerlimit of that range and any other stated or intervening value in thatstated range, is encompassed within the invention. The upper and lowerlimits of these smaller ranges may independently be included in thesmaller ranges, and are also encompassed within the invention, subjectto any specifically excluded limit in the stated range. Where the statedrange includes one or both of the limits, ranges excluding either orboth of those included limits are also included in the invention.

Unless defined otherwise, all technical and scientific terms used hereinhave the same meaning as commonly understood by one of ordinary skill inthe art to which this invention belongs. Although any methods andmaterials similar or equivalent to those described herein can also beused in the practice or testing of the present invention, the preferredmethods and materials are now described. All publications mentionedherein are incorporated herein by reference to disclose and describe themethods and/or materials in connection with which the publications arecited.

It must be noted that as used herein and in the appended claims, thesingular forms “a,” “and,” and “the” include plural referents unless thecontext clearly dictates otherwise. Thus, for example, reference to “ahemostatic agent” includes a plurality of such agents and reference to“the hemostatic agent” includes reference to one or more agents andequivalents thereof known to those skilled in the art, and so forth. Itis further noted that the claims may be drafted to exclude any optionalelement. As such, this statement is intended to serve as antecedentbasis for use of such exclusive terminology as “solely,” “only” and thelike in connection with the recitation of claim elements, or use of a“negative” limitation. Moreover any positively recited element of thedisclosure provides basis for a negative limitation to exclude thatelement from the claims.

The publications discussed herein are provided solely for theirdisclosure prior to the filing date of the present application. Nothingherein is to be construed as an admission that the present invention isnot entitled to antedate such publication by virtue of prior invention.Further, the dates of publication provided may be different from theactual publication dates which may need to be independently confirmed.

DETAILED DESCRIPTION

Embodiments of the present disclosure relate to hemostatic compositionsthat include a hemostatically effective amount of a hemostatic agentthat includes a nanoparticle and a polyphosphate polymer attached to thenanoparticle. Also provided are medical devices and methods of use topromote blood clotting.

Hemostatic Agents

Aspects of the present disclosure include biologically active agentsconfigured to promote blood clotting. These hemostatic agents include ananoparticle and a polyphosphate polymer attached to the nanoparticle.By “nanoparticle” is meant a particle that has dimensions in thenanometer scale, such as dimensions of 1000 nm or less, such as 750 nmor less, including 500 nm or less, or 250 nm or less, or 200 nm or less,or 150 nm or less, or 100 nm or less, or 50 nm or less, or 40 nm orless, or 30 nm or less, or 25 nm or less, or 20 nm or less, or 15 nm orless, or 10 nm or less, or 5 nm or less. In some instances, thenanoparticle has dimensions of 100 nm or less. The term “average” asused herein is meant to be the arithmetic mean.

In certain embodiments, the nanoparticle is spherical in shape, althoughin other embodiments, other shapes of the nanoparticle may also beincluded. For example, some embodiments of the nanoparticle have a shapesuch as, but not limited to, an ellipsoid, a rod, a cone, a cube, acuboid (e.g., a rectangular box), a pyramid, an irregular shape, etc. Incertain instances, combinations of different shapes of nanoparticles maybe included. As indicated above, the nanoparticle may be substantiallyspherical in shape, and thus may have dimensions measured as a diameterof the sphere, such as an average diameter of 1000 nm or less, such as750 nm or less, including 500 nm or less, or 250 nm or less, or 200 nmor less, or 150 nm or less, or 100 nm or less, or 50 nm or less, or 40nm or less, or 30 nm or less, or 25 nm or less, or 20 nm or less, or 15nm or less, or 10 nm or less, or 5 nm or less. In some instances, asubstantially spherical nanoparticle has an average diameter of 100 nmor less.

In certain embodiments, the nanoparticle is non-porous. By “non-porous”is meant that the nanoparticle is substantially solid, such that theaccessible surface (e.g., solvent accessible surface, such as anexterior surface of the particle the may be contacted by a surroundingfluid) of the nanoparticle is the exterior surface of the nanoparticle.In some instances, a non-porous nanoparticle does not have pores exposedon the surface of the nanoparticle. In other embodiments, thenanoparticle is porous. A porous nanoparticle may have one or more poresexposed on the surface of the nanoparticle, such that the accessiblesurface of the nanoparticle includes the exterior surface of thenanoparticle and the interior surfaces of the one or more pores withinthe nanoparticle. In certain cases, a porous nanoparticle has a greateraccessible surface area than a non-porous nanoparticle of the same shapeand average dimensions.

The pore size of a porous nanoparticle can be selected to provide fordesired clot-promoting activity (e.g., clotting rate, clotting time,clot strength, etc.). Average pore size is generally determined by theBET-BJH calculation of N₂ desorption/adsorption isotherm data. In someembodiments, the average pore size of a porous nanoparticle ranges from1 to 100 nm, such as 1 nm to 75 nm, including 1 nm to 50 nm, or 5 nm to50 nm, or 5 nm to 40 nm, or 5 nm to 30 nm, or 10 nm to 30 nm. In certaincases, the average pore size of the porous nanoparticle is from 10 nm to30 nm. In some embodiments, the porous nanoparticle has an average poresize of 1 nm or more, such as 5 nm or more, including 10 nm or more, or15 nm or more, or 20 nm or more, or 25 nm or more, or 30 nm or more, or35 nm or more, or 40 nm or more, or 45 nm or more, or 50 nm or more,with the proviso that the average pore size is 100 nm or less. Incertain embodiments, the porous nanoparticle has an average pore size of10 nm or more. In some embodiments, the porous nanoparticle may have anaverage pore size of 50 nm or less, such as 45 nm or less, including 40nm or less, or 35 nm or less, or 30 nm or less, or 25 nm or less, or 20nm or less, or 15 nm or less, or 10 nm or less, or 5 nm or less, or 1 nmor less. In certain embodiments, the porous nanoparticle may have anaverage pore size of 30 nm or less.

In certain embodiments, the nanoparticle is composed of an oxide ofsilicon, aluminum, a transition metal (e.g., titanium, zirconium, andthe like), aluminosilicate, or combination thereof. Exemplary materialsfor the nanoparticle include, but are not limited to, silicon dioxide(e.g., silica), titanium dioxide, silicon-aluminum-oxide, aluminumoxide, iron oxide, polymers (e.g., polystyrene), metals (e.g., gold),and the like. In some instances, the nanoparticle is composed of otherinorganic materials, such as, but not limited to, diatomaceous earth,calcium hydroxyapatite, and the like. Combinations of the abovematerials may also be included.

In certain embodiments, the nanoparticle is a thermal treatednanoparticle. For example, the nanoparticle may be treated at hightemperature, such as in a calcination process. In some instances, thenanoparticles are treated (e.g., calcined) at a temperature of 200° C.or more, such as 250° C. or more, or 300° C. or more, or 350° C. ormore, or 400° C. or more, or 450° C. or more, or 500° C. or more, or550° C. or more, or 600° C. or more, or 650° C. or more, or 700° C. ormore, or 750° C. or more. In certain embodiments, the nanoparticles aretreated (e.g., calcined) at a temperature of 250° C. In certainembodiments, the nanoparticles are treated (e.g., calcined) at atemperature of 550° C. In some instances, thermal treatment of thenanoparticles facilitates a reduction in the zeta potential of thenanoparticles. In some instances, a hemostatic agent with a lower zetapotential has increased hemostatic activity. In some cases, thehemostatic agent has a zeta potential of 0 mV or less, such as −1 mV orless, or −5 mV or less, or −10 mV or less, or −15 mV or less, or −20 mVor less, or −25 mV or less, or −30 mV or less. In certain embodiments,the hemostatic agent has a zeta potential of −15 mV or less.

In certain embodiments, the nanoparticle may have hemostatic activity,such that the nanoparticle promotes blood clotting (e.g., as compared toblood clotting in the absence of the hemostatic agent). As such, ananoparticle with hemostatic activity may be described as beinghemostatically effective. For example, without being limited to anyparticular theory, the nanoparticle may have a negative surface chargein body fluid (e.g., blood), which may facilitate activation of thecoagulation cascade by activating Factor XII. The promotion of bloodclotting may be described by one or more of the following factors: (1)reduction in initial time for blood clot formation (R, min); (2)increase in the rate of clot formation (α, deg); (3) increase in clotstrength or maximum amplitude (MA, mm); and (4) reduction in time untilclot reaches 20 mm (K, min).

As described above, in certain embodiments, the hemostatic agentincludes a polyphosphate polymer (polyP) attached to the nanoparticle.In certain instances, the polyphosphate polymer is hemostaticallyeffective to promote blood clotting (e.g., as compared to blood clottingin the absence of the hemostatic agent). For example, without beinglimited to any particular theory, the polyphosphate polymer mayfacilitate activation of the coagulation cascade through activation ofFactor Xa. As such, the polyphosphate polymer may facilitate bloodclotting through activation of a different target (e.g., enzyme orzymogen) in the coagulation cascade than the nanoparticle.

In some cases, a hemostatic agent that includes a polyphosphate polymerattached to a nanoparticle has a greater hemostatic activity than thenanoparticle itself. For instance, a hemostatic agent that includes apolyphosphate polymer attached to a nanoparticle may have a clottingtime, R, (e.g., time until first evidence of a clot is detected) asmeasured by thrombelastography that is less than the clotting time ofthe nanoparticle itself. In some cases, a hemostatic agent that includesa polyphosphate polymer attached to a nanoparticle has a clotting time,R, of 15 min or less, such as 10 min or less, or 5 min or less, or 4.5min or less, or 4 min or less, or 3.5 min or less, or 3 min or less, or2.5 min or less, or 2 min or less, or 1.5 min or less, or 1 min or less,or 0.5 min or less. In some embodiments, a hemostatic agent thatincludes a polyphosphate polymer attached to a nanoparticle has aclotting time, R, of 3 min or less. In some embodiments, a hemostaticagent that includes a polyphosphate polymer attached to a nanoparticlehas a clotting time, R, of 2.5 min or less. In some embodiments, ahemostatic agent that includes a polyphosphate polymer attached to ananoparticle has a clotting time, R, of 2 min or less. In someembodiments, a hemostatic agent that includes a polyphosphate polymerattached to a nanoparticle has a clotting time, R, of 1.5 min or less.In some embodiments, a hemostatic agent that includes a polyphosphatepolymer attached to a nanoparticle has a clotting time, R, of 1 min orless.

In certain embodiments, a hemostatic agent that includes a polyphosphatepolymer attached to a nanoparticle has a greater hemostatic activitythat the polyphosphate polymer itself. For example, a hemostatic agentthat includes a polyphosphate polymer attached to a nanoparticle mayhave a clotting time, R, (as described above) which is less than theclotting time of the polyphosphate itself. In some instances, ahemostatic agent that includes a polyphosphate polymer attached to ananoparticle may promote blood clotting with a shorter polyphosphatepolymer length as compared to polyphosphate alone (i.e., a freepolyphosphate polymer). For instance, a hemostatic agent that includes ashort (e.g., 100mer or less, such as 70mer) polyphosphate polymerattached to a nanoparticle may produce a significant reduction inclotting time as compared to a short polyphosphate polymer alone. Insome instances, the clotting time of a hemostatic agent that includes ashort (e.g., 100mer or less, such as 70mer) polyphosphate polymerattached to a nanoparticle may be less than or equal to the clottingtime of a long (e.g., 500mer or greater) polyphosphate polymer alone.

The polyphosphate polymer may be composed of two or more phosphatemonomers attached together to form the polyphosphate polymer. Forexample, the polyphosphate polymer may include 2 or more monomers, suchas 5 or more, including 10 or more, or 20 or more, or 30 or more, or 40or more, or 50 or more, or 60 or more, or 70 or more, or 80 or more, or90 or more, or 100 or more, or 150 or more, or 200 or more, or 250 ormore, or more, or 300 or more, or 400 or more, or 500 or more, or 600 ormore, or 700 or more, or 800 or more, or 900 or more, or 1000 or more,or 1100 or more, or 1200 or more, or 1300 or more, or 1400 or more, or1500 or more phosphate monomers. In certain cases, the polyphosphatepolymer composition includes an average of 70 phosphate monomers perpolymer. In other embodiments, the polyphosphate polymer compositionincludes an average of 700 phosphate monomers per polymer. Combinationsof different sized phosphate polymers may also be included. Forinstance, the polyphosphate polymer composition may have from 2 to 200phosphate monomers per polymer, such as from 5 to 200, including from 10to 200, or from 10 to 150, or from 10 to 100, of from 20 to 100, or from30 to 100, or from 40 to 100, or from 50 to 100 phosphate monomers perpolymer. In other instances, the polyphosphate polymer composition mayhave from 100 to 1500 phosphate monomers per polymer, such as from 100to 1400, or from 100 to 1300, or from 200 to 1300 phosphate monomers perpolymer.

In certain embodiments, the polyphosphate polymer is attached to thenanoparticle. For example, the polyphosphate polymer may be adsorbed onthe surface of the nanoparticle. The binding interaction can be based onone or more of a variety of binding interactions between thepolyphosphate polymer and the nanoparticle, such as, but not limited to,covalent bonds, ionic bonds, electrostatic interactions, hydrophobicinteractions, hydrogen bonds, van der Waals forces (e.g., Londondispersion forces), dipole-dipole interactions, combinations thereof,and the like. The polyphosphate polymer may be attached to thenanoparticle through a linking group between the nanoparticle surface orpores and the polyphosphate polymer. The binding interactions may besubstantially permanent (e.g., requiring a relatively large amount ofenergy to overcome the binding interaction, such as with covalent bonds)or may be reversible (e.g., requiring a relatively low amount of energyto disrupt the binding interaction, such as with dipole-dipoleinteractions). For example, the polyphosphate polymer may be attached tothe nanoparticle via a phosphoramidate bond, ester linkage, carboxylicacid linkage, or another form of linkage. In certain embodiments, bondsmay be altered in strength depending on factors present or arising inthe body (e.g., enzymes, fibrin, etc.), or affected by externallyapplied fields (e.g., magnetic, etc.), or by injection of a modifieragent directed at the polyphosphate polymer, linkage, or nanoparticle.

Embodiments of the hemostatic agent include a nanoparticle and apolyphosphate polymer, as described above. In certain embodiments, thehemostatic agent has a composition with a particular mass ratio of thepolyphosphate polymer to the nanoparticle. For instance, the hemostaticagent may have a polyphosphate polymer to nanoparticle mass ratio of1:10 or more, such as 1:9 or more, including 1:8 or more, or 1:7 ormore, or 1:6 or more, or 1:5 or more, or 1:4 or more, or 1:3 or more, or1:2 or more, or 1:1 or more, or 2:1 or more, or 3:1 or more, or 4:1 ormore, or 5:1 or more. In some embodiments, the hemostatic agent has apolyphosphate polymer to nanoparticle mass ratio of 1:2 or more, such as1:2. In some embodiments, the hemostatic agent has a polyphosphatepolymer to nanoparticle mass ratio of 1:1 or more, such as 1:1.

In certain embodiments, the hemostatic agent includes a protectingagent. The protecting agent may be substantially unreactive in the body,such as substantially unreactive towards elements of the coagulationcascade. The protecting agent may be configured to reduce or inhibit thehemostatic activity of the hemostatic agent. For example, in certaininstances, the protecting agent may be configured to block or cover theaccessible surface of the polyphosphate polymer, such that interactionsbetween the polyphosphate polymer and its target (e.g., enzyme orzymogen or fibrin surfaces) are reduced or inhibited. This reduction orinhibition in the interaction between the polyphosphate polymer and itstarget may be sufficient to facilitate a reduction in the activation ofthe target as compared to when the protecting agent is not present. Forexample, a hemostatic agent that includes a protecting agent may havesubstantially no hemostatic activity, such that the hemostatic agentthat includes a protecting agent does not significantly promote bloodclotting as compared to blood clotting in the absence of the hemostaticagent.

In certain embodiments, the protecting agent is attached to thehemostatic agent. In some cases, the protecting agent is removablyattached to the hemostatic agent. In these embodiments, the protectinggroup may be attached to the hemostatic agent and then may besubsequently detached (e.g., cleaved) from the hemostatic agent torelease the hemostatic agent from the protecting agent. When theprotecting agent is removed from the hemostatic agent, the polyphosphatepolymer attached to the surface of the nanoparticle may be exposed, andthus may be accessible for interactions with its target as describedabove. In these embodiments, a removable protecting agent may facilitateactivation of the hemostatic agent at a desired site of action, e.g., ahemorrhage site, such as an internal hemorrhage site in a subject. Forexample, removal of the protecting group from the hemostatic agent mayproduce a free hemostatic agent that has hemostatic activity, such thatthe free hemostatic agent promotes blood clotting as compared to bloodclotting in the presence of the hemostatic agent attached to theprotecting group (or as compared to blood clotting in the absence of thehemostatic agent).

In certain embodiments, the protecting agent is attached to thenanoparticle. In some instances, the protecting agent is attached to thepolyphosphate polymer. The protecting agent may be attached to the endof the polyphosphate polymer, or attached to a fraction of the phosphateoxygen atoms in the polyphosphate polymer. In certain cases, theprotecting agent is attached to the hemostatic agent at a combination ofsites including the nanoparticle and the polyphosphate polymer (e.g.,the end of the polyphosphate polymer and/or an internal binding site).The protecting group can be covalently or non-covalently associated tothe hemostatic agent using a mediator having affinity to thenanoparticle (e.g., silica) or polyphosphate (e.g., phosphoramidatelinkage). The mediator may be cleaved by one or more proteases. Themediator can be composed of alternating repeats of affinity parts,linkers, and cleavable parts. In certain instances, the summary affinity(avidity) is stronger than any partially cleaved product. The mediatorcan also be crosslinked to other mediators in the hemostatic agent,either covalently or non-covalently.

In certain instances, the protecting agent is composed of a polymer. Thepolymer may be configured to be substantially unreactive in the body,such as substantially unreactive towards elements of the coagulationcascade. As such, the polymer may be configured to reduce or inhibit thehemostatic activity of the hemostatic agent as described above. In someinstances, the protecting agent includes a polyethylene glycol (PEG)polymer. The PEG polymer may be branched or unbranched as desired, aslong as the function of the PEG polymer is maintained as describedabove. In some cases, the PEG polymer has an average molecular mass of1000 Da or more, such as 1500 Da or more, including 2000 Da or more, or3000 Da or more, or 4000 Da or more, or 5000 Da or more, or 6000 Da ormore, or 7000 Da or more, or 8000 Da or more, or 9000 Da or more, or10,000 Da or more, or 15,000 Da or more, or 20,000 Da or more. Incertain instances, the PEG polymer has an average molecular mass of 2000Da. In certain instances, the PEG polymer has an average molecular massof 1000 Da.

In certain embodiments, the mass ratio of PEG to polyphosphate rangesfrom 1:1000 to 1000:1, such as from 1:900 to 900:1, including from 1:800to 800:1, or from 1:700 to 700:1, or from 1:600 to 600:1, or from 1:500to 500:1, or from 1:400 to 400:1, or from 1:300 to 300:1, or from 1:200to 200:1, or from 1:100 to 100:1, or from 1:75 to 75:1, or from 1:50 to50:1, or from 1:25 to 25:1, or from 1:10 to 10:1, or from 1:5 to 5:1. Insome instances, the mass ratio of PEG to polyphosphate ranges from 1:50to 50:1. In certain embodiments, the protecting agent is composed of oneor more of the following: PEG; polyvinylpyrrolidone (PVP);poly(lactic-co-glycolic acid) (PLGA); polypropylene glycol;poly(carboxybetaine); poly(sulfobetaine); poly(carboxybetainemethacrylate) (PCBMA); polyoxamers; polypeptides; biodegradablematerials such as polylactonic acid and its derivatives, collagens,albumin, gelatin, hyaluronic acid, starch, cellulose (e.g.,methylcellulose, hydroxypropylcellulose, hydroxypropylmethylcellulose,carboxymethylcellulosephthalat, casein, dextrane, polysaccharides,fibrinogen, poly(D,L-lactide), poly(D,L-lactide-co-glycolide), and thelike; polyurethanes; poly(ethylene vinyl acetate); silicones; acrylicpolymers like polyacrylic acids, polymethylacrylic acid,polyacrylcyanoacrylate; polyethylene; polypropylene; polyamide;poly(ester urethane); poly(ether urethane); poly(ester urea); polyetherssuch as polyethylene oxide, polypropylene oxide, pluronics,polytetramethylene glycol; vinyl polymers such as polyvinylpyrrolidone,poly(vinyl alcohol), poly(vinylacetatephthalate); parylenes;polyurethane; poly(hydroxybutylate); poly(alkyl carbonates);poly(orthoesters); polyesters; poly(hydroxyvaleric acid); polydioxanone;poly(ethylene terephthalate); poly(malic acid); poly(tartronic acid);polyanhydrides; polyphosphohazenes; and the like, or copolymers thereof.Polymer variations are further described in EP 1830902 A2, thedisclosure of which is incorporated herein by reference.

In certain embodiments, the protecting agent is attached to thehemostatic agent by a linking group. In some cases, the linking group isan enzymatically-cleavable linking group. For example, the linking groupmay be an enzymatically-cleavable peptide linking group. The cleavablepeptide linking group may be configured such that it is specificallyrecognized and cleaved by a target enzyme. For instance, the targetenzyme may be an enzyme that has an activity localized to a particulararea(s) in a subject, such as a particular target site of action for thehemostatic agent. In some cases, the target enzyme may have an activitylocalized to a hemorrhage site in a subject, such as an internalhemorrhage site in a subject or an external hemorrhage site in asubject. For example, the enzymatically-cleavable linking group may beconfigured such that it is specifically cleaved by one or more enzymesinvolved in the coagulation cascade, such as, but not limited to,thrombin (Factor IIa), Factor VIIa, Factor IXa, Factor Xa, FactorXia,Factor Xia, Factor XIIa, Factor XIIIa, tissue plasminogen activator(tPA), urokinase plasminogen activator (uPA), activated protein C,plasmin, and the like.

In these embodiments, the corresponding protected hemostatic agentprovides post administration-activated, controlled release of thehemostatic agent, because it requires enzymatic cleavage to initiaterelease of the hemostatic agent from the protecting group. In certaininstances, the rate of release of the hemostatic agent depends upon therate of enzymatic cleavage at the target site of action. Accordingly,the protected hemostatic agent can be configured such that it does notprovide significant plasma levels of the active hemostatic agent and isnot readily decomposed to afford the biologically active hemostaticagent other than by enzymatic cleavage at the target site of action.

The enzyme capable of cleaving the enzymatically-cleavable linking groupmay be a peptidase—the enzymatically-cleavable linking group beinglinked to the hemostatic agent through an amide (e.g., a peptide:—NHCO—) bond. In some embodiments, the enzyme is a peptidase such asthose involved in the coagulation cascade. Examples include Factor Xa,FactorXia, Factor VIIa, and thrombin, and the like.

The enzymatically-cleavable linking group attached to the hemostaticagent through an amide bond may be, for example, a residue of an aminoacid or a peptide. The peptide may contain, for example, up to 10 aminoacid residues. For example, it may be a dipeptide or tripeptide. Incertain embodiments, each amino acid is an L-amino acid. Examples ofnaturally occurring amino acids are alanine, arginine, asparagine,aspartic acid, cysteine, glycine, glutamine, glutamic acid, histidine,isoleucine, leucine, methionine, phenylalanine, proline, serine,threonine, tryptophan, tyrosine, lysine and valine. Accordingly,examples of enzymatically-cleavable linking groups include residues ofthe L-amino acids listed above and dipeptides and tripeptides, or longerpeptides, formed from the L-amino acids listed above.

In certain embodiments, the enzymatically-cleavable linking group isattached to the nanoparticle, such as covalently bound to thenanoparticle. The enzymatically-cleavable linking group may becovalently bound to the surface of the nanoparticle using any of avariety of compounds typically used to functionalize the surface ofmolecules, such as, but not limited to, silanization reagents, such asan aminosilane, e.g., (3-aminopropyl)triethoxysilane (APTES), and thelike. In certain embodiments, the ratio of silanization reagent (e.g.,APTES) to nanoparticle is 1.5 μL/g or more, such as 1.6 μL/g or more,including 1.7 μL/g or more, or 1.8 μL/g or more, or 1.9 μL/g or more, or2 μL/g or more. In some cases, the ratio of silanization reagent (e.g.,APTES) to nanoparticle ranges from 1.5 μL/g to 2 μL/g, such as from 1.6μL/g to 2 μL/g.

In certain embodiments, the hemostatic agent may include a specificbinding agent. A specific binding agent can be any molecule thatspecifically binds to a protein or nucleic acid sequence orbiomacromolecule that is being targeted (e.g., a target located at atarget site of interest, such as a hemorrhage site). Depending on thenature of the target, a specific binding agent can be, but is notlimited to, an antibody against an epitope of a peptide target, or anyrecognition molecule, such as a member of a specific binding pair. Forexample, suitable specific binding pairs include, but are not limitedto: a member of a receptor/ligand pair; a ligand-binding portion of areceptor; a member of an antibody/antigen pair; an antigen-bindingfragment of an antibody; a hapten; a member of a lectin/carbohydratepair; a member of an enzyme/substrate pair; biotin/avidin;biotin/streptavidin; digoxin/antidigoxin; a member of a peptide aptamerbinding pair; and the like. For example, a specific binding agent may bea part of the protecting agent, which may be configured to bind to cellsor surfaces in the blood, or vessel walls, or tissues, thereby alteringthe dispersement or concentration of the hemostatic agent in thesubject. Affinity may be derived from groups within or attached to theprotecting agent (e.g., on the end of PEG), or may be derived from thepolyphosphate component, or a specific binding agent separate from theprotecting agent (e.g., separately bound to the nanoparticle or thepolyphosphate polymer).

Examples of a specific binding agent include, but are not limited to: afibrin binding ligand (e.g., a fibrin binding peptide such as CREKA (SEQID NO: 1), a fibrin binding aptamer, a fibrin binding protein, a fibrinbinding antibody, etc.); a collagen binding peptide (e.g., KLWVLPK (SEQID NO: 2)); an affinity ligand for activated platelets,thrombomodulin/thrombin complexes, specific endothelial cells (e.g.,activatable peptide from thrombin-activatable fibrinolysis inhibitor(TAFI), tissue factor, lipid membranes, and the like; an enzyme with anexposed fibrin binding motif; a ligand configured to form a covalentbond to fibrin (e.g., alpha2AP N-terminal peptide H-NQEQVSPLTGLK-NH₂(SEQ ID NO: 3)); a thrombin binding ligand (e.g., a thrombin bindingaptamer or peptide); antibody domains; inhibitors (e.g., peptides with areactive ketone, etc.); combinations thereof, and the like.

Additional Agents for Use with the Hemostatic Agent in a HemostaticComposition

The hemostatic agents disclosed herein can be provided alone as ahemostatic composition or can be provided in combination with one ormore additional biologically active agents (e.g., hemostatic agents,antibiotics, ions (e.g., calcium, potassium, etc.) and the like) in ahemostatic composition. In general, optionally additional agents caninclude components which may be active or inert with respect to theactivity of the hemostatic composition in promoting blood clotting, ormay provide for an additional or different biological activity (e.g.,antibacterial, anti-inflammatory, and the like). Such additionalagent(s) can be provided in admixture (e.g., in dry or hydrated (e.g.,solution)) with the hemostatic agent (e.g., in a slurry) or provided onthe surface (e.g., for a non-porous hemostatic agent) or loaded into thehemostatic agent structure itself (e.g., for a porous hemostatic agent).

In some embodiments, the hemostatic composition includes an additionalbiologically active agent that can facilitate blood clotting, woundhealing, and/or reduce the risk of infection. Such exemplary additionalagents can include an agent with hemostatic activity, an antibiotic, agrowth factor, a cytokine, and the like, which can promote wound healingand/or reduce the risk of infection. Such components can be from anysuitable source, e.g., a recombinant source of the same or differentanimal origin as the subject to be treated (e.g., human, bovine, etc.).The hemostatic agent can be loaded with the biologically active agent toprovide for biological activity as a varying weight percent of thehemostatic composition, e.g., 1% or more, 2% or more, 5% or more, 10% ormore, 15% or more, 20% or more, 25% or more, or even greater weightpercentages, depending on the biologically effective amount needed toproduce the desired effect in the subject.

In some embodiments, the hemostatic composition includes aclot-promoting factor in addition to the hemostatic agent describedherein. For example, the hemostatic composition can include a clottingfactor or platelet activating agent. Exemplary agents include thrombin,Factor VII, Factor VIIa, serotonin, collagen, thromboxane A2, and ADP,combinations thereof, and the like. Such components can be from arecombinant source of the same or different animal origin as the subjectto be treated (e.g., human, bovine, etc.).

In some embodiments, the hemostatic agent in the hemostatic compositionis modified to include a bound biologically active agent, which may be aprotein, an ion, or the like. Agents that have hemostatic activity areof interest. For example, a surface (e.g., external and/or internalsurface) of the hemostatic agent may be modified to provide for a boundclot-promoting factor (e.g., thrombin, recombinant Factor VIIa, etc.),an antibiotic (e.g., silver ions), and the like. “Bound” as used in thiscontext (which may be used interchangeably with the term “loaded”) ismeant to encompass covalent and non-covalent binding, including van derWaals forces, hydrogen bonds, chemisorption, physisorption,electrostatic forces, physical trapping within pores and/or channels ofthe hemostatic agent, and the like. Thus an agent that is “bound” to asurface of the hemostatic agent includes binding by absorption,adsorption, adhesion, covalent linkage, and the like.

Biologically active agent-loaded hemostatic agent can be produced by avariety of different methods. For example, the hemostatic agent can besoaked in a solution containing one or more agents of interest toprovide for adsorption of the agent(s) onto a surface (e.g., externaland/or internal surface) of the hemostatic agent. Following soaking fora desired period of time (e.g., to provide for a desired amount of agentloaded on and/or into the hemostatic agent), the biologically activeagent-loaded hemostatic agent can then be washed to remove unboundmaterial. The loaded hemostatic agent can then be dried or stored inhydrated or partially hydrated form, as may be desired according to thebiologically active agent used.

In another example, the hemostatic agent can be heat treated to presenta hydroxylated surface for condensation attachment of an oxo- orhydro-group expressing biologically active agents. This productionmethod can provide for covalent binding of biologically active agent(e.g., protein, polyphosphate, silananizing agent, hydroxyl-PEG) to anexternal and/or internal surface of the hemostatic agent.

In another example, the surface of the hemostatic agent may befunctionalized with, e.g., organosilanes, amino acids, carboxylic acids,esters and/or phosphate groups, to promote the non-covalent or covalentbinding of an active agent. For example, the hemostatic agent can befunctionalized with amine groups (e.g., primary, secondary or tertiary)to express a positive surface charge capable of electrostaticallyattracting negatively charged substituents in solution. Alternatively,the hemostatic agent can be functionalized with carboxylate groups toexpress a negative surface charge capable of electrostaticallyattracting positively charged substituents in solution. Other chemicalgroups that increase, decrease, or neutralize surface charge may beemployed.

In another example, the oxide surface of the hemostatic agent can befunctionalized with, e.g., organosilanes, amino acids, amines,carboxylic acids, and/or phosphate groups, to promote the attachment ofbiologically active materials. For example, silicon dioxide may expressa negative surface charged when immersed in a solution with a pH greaterthan the isoelectric point of silicon dioxide. However, if silicondioxide is first functionalized by attaching amine groups to the surfaceof silicon dioxide, the effective surface charge may be positive as aconsequence of the positively charged amine groups on the periphery.Amine functionalized silica may electrostatically attract negativelycharged substituents. Negatively charged silica, absent amine functionalgroups, may electrostatically repel negatively charged substituents.

Biologically active agents that find use in the hemostatic compositionof the present disclosure, and which may used to provide a biologicallyactive agent-loaded hemostatic agent can be selected from a variety ofdifferent active agents. Exemplary active agents include, but are notlimited to, polypeptides (e.g., enzymes (including zymogens andactivated enzymes), glycoproteins, peptides, and the like),phospholipids, ions, such as ions that act as cofactors in the clottingcascade (e.g., by serving as an ionic bridge) and/or ions thatfacilitate colloid precipitation (e.g., red blood cell precipitation),and/or ions that have antibiotic activity (e.g., silver ions), and thelike), and other active agents that have a biological activity ofinterest (e.g., clot-promoting agents, antibiotics, anti-inflammatories,and the like). Where the active agent is a polypeptide or nucleic acid,the agent may be recombinant or synthetic (e.g., produced by non-geneticmethods). Of interest are active agents that have activity in promotingblood clotting (e.g., thrombin) and/or antibacterial activity (e.g.,silver ions). Biologically active agents, such as polypeptides, can beof any suitable origin, e.g., human, bovine, etc.

Exemplary biologically active polypeptide agents include, but are notlimited to, prothrombin, thrombin, Factor VII, Factor VIIa, Factor X,Factor Xa, Factor XI, Factor XIa, Factor XII, Factor XIIa, Factor XIII,Factor XIIIa, fibrin, collagen, fibrinogen, growth factors (e.g.,vascular endothelial growth factor (VEGF), epidermal growth factors,fibroblast growth factors, transforming growth factors, and the like),prekallikrein, high molecular weight-kininogen, protein concentrates(e.g., clotting factor concentrates (e.g., alphanate FVIII concentrate,bioclate FVIII concentrate, monoclate-P FVIII concentrate, haemate PFVIII, von Willebrand Factor concentrate, helixate FVIII concentrate,hemophil-M FVIII concentrate, humate-P FVIII concentrate, hyante-C™,Porcine FVIII concentrate, koate HP FVIII concentrate, kogenate FVIIIconcentrate, FVIII concentrate, mononine FIX concentrate, fibrogammin pFXIII concentrate, and the like), combinations thereof, and biologicallyactive fragments thereof. It should be noted that the term “biologicallyactive polypeptide agents” is meant to encompass active (e.g.,processed) as well as activatable forms (e.g., zymogen) forms ofpolypeptides (e.g., where the polypeptides is an enzyme).

Exemplary ions that find use as a biologically active agent include, butare not necessarily limited to, Ca²⁺, Mg²⁺, Ag⁺, Na⁺, Zn²⁺, PO₄ ³⁻, SO₄²⁻, NO₃ ⁻, and the like. Such ions can be provided in the form of asalt, e.g., a salt-loaded hemostatic agent.

Exemplary salts that find use in the hemostatic compositions include,but are not limited to, aluminum sulfate, silver nitrate, calciumchloride, magnesium chloride, and the like. In certain embodiments, thehemostatic composition may include silver nitrate.

Exemplary anti-inflammatory agents that find use in the hemostaticcompositions disclosed herein include, but are not necessarily limitedto, leukocyte migration preventing agents, silver sulfadiazine,acetylsalicylic acid, indomethacin, nafazatrom, and the like.

Other biologically active agents that can find use in the hemostaticcompositions disclosed herein include, but are not limited to,antibiotics (e.g., bacteriocides, bacteristatics, fungicides,antivirals, and the like). Examples of such active agents include, butare not limited to, Ag⁺ ions, which may be provided as a silver salt,e.g. AgNO₃; β-lactams, cefoxitin, n-formamidoyl thienamycin, thienamycinderivatives, neomycin, metronidazole gramicidin, bacitracin,sulfonamides, aminoglycosides such as gentamycin, kanamycin, amikacin,sisomicin, or tobramycin, nalidixic acids and analogs such asnorfloxican, combinations of fluoroalanine/pentizidone, nitrofurazones,combinations thereof, and the like. Such antibiotics are generallyselected so as to be compatible with the site of delivery (e.g., type ofhemorrhage site to be treated, the site of the wound, and the like), andthe microbial infection to be prevented and/or treated.

Further exemplary biologically active agents may include analgesics,anesthetics, steroids, vasoconstrictors, lymphokines, cytokines,vitamins, and the like.

Hemostatic Compositions and Devices

As noted above, the hemostatic agent can be provided alone or incombination with one or more additional biologically active agents.Where the hemostatic composition is composed of a hemostatic agent withone or more additional biologically active agents, such hemostaticcompositions may be provided in a variety of formats. For example, thebiologically active agents of the hemostatic composition may be providedas a mixture (e.g., blended or admixed), may be provided as a coating ona substrate (e.g., where one or both of the biologically active agentand/or hemostatic agent is provided as a coating adhered to asubstrate), or may be provided in a single package in the same orseparate compartments of the package. The hemostatic agent and theadditional biologically active agent(s) may also be provided in two ormore packages that are to be opened and administered simultaneously(e.g., concurrently or consecutively) to a hemorrhage site.

In certain embodiments, the hemostatic composition includes a hemostaticagent, as described herein. In some instances, the hemostatic agentincludes a nanoparticle and a polyphosphate polymer attached to thenanoparticle, as described herein. In some instances, the hemostaticagent includes a nanoparticle, a polyphosphate polymer attached to thenanoparticle, and a protecting agent attached to the nanoparticle orpolyphosphate polymer by an enzymatically-cleavable linking group, asdescribed herein. In some instances, the hemostatic composition includesa first hemostatic agent that includes a nanoparticle and apolyphosphate polymer attached to the nanoparticle, and a secondhemostatic agent that includes a nanoparticle, a polyphosphate polymerattached to the nanoparticle, and a protecting agent attached to thenanoparticle or polyphosphate polymer by an enzymatically-cleavablelinking group.

In general, a hemostatic composition can be provided as a sterilecomposition, and as such are generally provided in a sealed, sterilecontainer which maintains the sterility of the hemostatic compositionuntil use. Where desired, the container can further provide formaintenance of a hydration state of the hemostatic composition, e.g.,through use of materials that provide a water vapor-resistant barrier(e.g., mylar, plastic, etc.). For example, the hemostatic compositioncan be provided in a sterile container in the form of a sealable mylarfoil bag.

The hemostatic composition may further include fillers (e.g., aluminumsulfate) or thickening agents that facilitate the selective applicationof the hemostatic composition in various forms (e.g., as a paste, gel,powder, spray, aerosol, cement, or erodable (e.g., biodegradable) solidmember). For example, in certain embodiments, the hemostatic compositionmay be configured for administration to an external hemorrhage site, andthus may be in various forms, such as a paste, gel, powder, spray,aerosol, cement, or erodible composition as described above. In otherembodiments, the hemostatic agent may be configured for administrationto an internal hemorrhage site. In these instances, the hemostaticcomposition may be administered in a form compatible to intravenousadministration of the hemostatic composition, such as an aqueous,injectable formulation (e.g., a solution, a suspension, and the like).

Dosage Forms and Carriers

The hemostatic composition of the present disclosure can be provided ina variety of dosage forms, and, optionally, can be provided incombination with a variety of different, compatible carriers. Exemplarycarriers include those which facilitate application to a hemorrhagesite, such as an external wound, e.g., by facilitating delivery of thehemostatic composition from its packaging to a wound, facilitatingapplication and/or maintenance at a wound site, and the like.Accordingly, the hemostatic composition, where compatible with thehemostatic activity of the hemostatic composition, can be provided as adry formulation (e.g., a powder or other formulation that does notcontain a liquid as a carrier), a paste, gel, or the like. In someembodiments, the hemostatic composition is provided as a dry, flowabledosage form that can be dispensed from a container (e.g., from a pouchor other sealed container). The hemostatic composition can also beprovided in aerosol form, and thus can be provided in a sterile spray(e.g., which can be provided in combination with a propellant, or in asprayable solution). Hemostatic compositions can be stored in a suitablesterile container, e.g., in a water vapor-resistant container,optionally under an air-tight and/or vacuum seal. In other embodiments,where the hemostatic composition is configured for administration to aninternal hemorrhage site, the dosage form may include a carrier suitablefor intravenous administration of the hemostatic composition, such as anaqueous solution, saline solution, buffer solution, blood substitute,and the like.

Hemostatic Devices

The hemostatic composition disclosed herein can be provided inconnection with a device adapted for storage and/or delivery of ahemostatic composition to a hemorrhage site. As discussed above, thehemostatic composition is generally provided in a sterile container,which may further provide a water and/or vapor resistant barrier toprevent hydration of the hemostatic composition, as may be desired.

The container can be in the form of a pouch (e.g., a mylar pouch),canister, tube, or other container. The container can include afrangible portion to facilitate rapid opening of the container toprovide for quick access to and delivery of the hemostatic compositioncontained therein. For solution-based formulations, the container mayinclude a bag, pouch, vial, bottle, or other container suitable forcontaining a liquid formulation. For example, the container may includean IV bag configured for intravenous administration of the hemostaticcomposition, or a sealed vial from which a desired dose of thehemostatic composition may be withdrawn, e.g., via a syringe, foradministration to the subject.

The hemostatic composition can be provided in conjunction with a varietyof different devices, which can be adapted to facilitate administrationof the hemostatic composition to a hemorrhage site. For example, thehemostatic composition can be packaged in the same or separate containerwith one or more of a sterile sponge, gauze, bandage, swab, spray,aerosol, gel, cement, compression bandage, pillow (e.g., to facilitateapplication to a head wound), sleeve (e.g., for covering a wound on alimb), and the like. In some embodiments, the device serves as asubstrate for the hemostatic composition, where the hemostatic agent inthe hemostatic composition can be adhered to the device. For example,the hemostatic composition can be provided on a blood-accessible surfaceof the device (e.g., as a surface coating), and/or within the device(e.g., permeating at least a portion of an absorbent material, such asgauze). It is to be understood that a “coating” is at least on thesurface of the substrate to which it is applied, and may permeate beyondthe surface, such as where the substrate is an absorbent material.

Where the hemostatic composition contains the hemostatic agent and oneor more additional biologically active agent, the hemostatic agent andother agent(s) may be present as a loose mixture (e.g., as in a pouch tobe opened prior to use). In certain embodiments, one or morebiologically active agents are loaded on a hemostatic agent in thehemostatic composition. In other embodiments, the hemostatic compositionis provided as a coating on a substrate, where the hemostatic agent maybe optionally loaded with a biologically active agent (e.g., thrombin).Alternatively or in addition, the hemostatic agent may be provided as acoating on a substrate (e.g., bandage or sponge) and a secondbiologically active agent may be provided loose and in the same sealedpackaging as the substrate.

Where the hemostatic composition is configured for administration to aninternal hemorrhage site, the hemostatic composition may include thehemostatic agent and one or more additional biologically active agents,where the hemostatic agent and other agent(s) may be present in the samesolution (or suspension). In certain embodiments, one or morebiologically active agents are loaded on a hemostatic agent in thehemostatic composition, and thus may be provided in a single solution(or suspension). In other embodiments, the other active agent(s) may beprovided in separate containers from the hemostatic composition and maybe administered simultaneously (e.g., concurrently or consecutively) tothe subject.

Methods of Use of Hemostatic Compositions and Devices

The hemostatic compositions disclosed herein can be used to facilitateclotting of an internal or external bleeding wound. As such, thehemostatic compositions can be used to enhance blood clotting at ahemorrhage site of a subject in need thereof, and at least temporarilystabilize a wound (e.g., at least temporarily stabilize a patient thatmight otherwise have died as a result of exsanguinations). Such methodsgenerally involve contacting a hemostatic composition disclosed hereinto a bleeding external or internal wound of a subject for a timesufficient to promote blood clot formation. As such, the method mayinclude administering to a hemorrhage site in a subject the hemostaticcomposition as described herein for a period of time sufficient to atleast initiate blood clotting at the hemorrhage site.

The hemostatic composition can be contacted with a wound that isexternally accessible by, for example, accessing the wound and pouringthe hemostatic composition onto the wound. Alternatively or in addition,the hemostatic composition can be delivered to an external wound byapplying a hemostatic device to the wound, where the device includes ahemostatic composition coated on a substrate. Contact can be maintainedthrough application of pressure, and may be held in place either by handand/or through use of a bandage. Contact may be maintained at leastuntil blood flow from the wound has slowed or has detectably ceased,i.e., until the wound is stabilized through formation of a clot. Oncethe clot is formed, the hemostatic composition can be removed from thewound. Where necessary, the wound can be irrigated to remove any loosehemostatic agent in the wound.

Where the hemostatic composition is configured for administration to aninternal hemorrhage site, the method may include intravenouslyadministering the hemostatic composition to the subject. As such, themethod may include locating an appropriate intravenous site on thesubject and injecting the hemostatic composition into the subject at theintravenous site. In certain embodiments, as described herein, thehemostatic agent may include a protecting agent that is configured toreduce or inhibit the hemostatic activity of the hemostatic agent. Uponinjection of the protected hemostatic agent into the subject, thehemostatic agent may circulate through the body of the subject untilactivated at a target site (e.g., a target internal hemorrhage site). Asdescribed above, the protecting agent may be removed from the hemostaticagent through cleavage of a cleavable linking group by an enzymelocalized at the target site, thus restoring the hemostatic activity ofthe hemostatic agent at the desired target site. In certain embodiments,the protecting agent is not significantly removed at other non-specificsites in the subject, such that the protected hemostatic agent does nothave detectable non-specific hemostatic activity at other sites in thesubject, and thus only has detectable hemostatic activity whenspecifically activated at the desired target site (e.g., the desiredtarget internal hemorrhage site).

These methods are applicable to a variety of different types of wounds,which may have been inflicted intentionally or through accident and atany portion of the body amenable to application of a hemostaticcomposition disclosed herein. The hemostatic composition finds use inwounds of all degrees of severity ranging from bleeding skin surfacewounds to wounds involving laceration of the femoral artery or othermajor artery or vein.

Subjects include any subject in need of treatment at an external orinternal hemorrhage site, and can include both human and veterinaryapplications (e.g., mammals such as dogs, cats, livestock (e.g., cattle,horses, sheep, goats, etc.), and the like).

Utility

The subject hemostatic compositions, devices and methods find use in avariety of different applications where the treatment of an external orinternal hemorrhage site in a subject is desired. In some instances, thewound may be an external hemorrhage site. In other embodiments, thewound may be an internal hemorrhage site. In some instances, the woundmay include both external and internal hemorrhage sites. The wound maybe a surgical wound or a trauma wound, such as, but not limited to, asurgical or traumatic soft tissue wound.

As described herein, the subject hemostatic compositions, devices andmethods find use in promoting blood clotting at a hemorrhage site,whether an external or internal hemorrhage site. In certain embodiments,the subject hemostatic compositions, devices and methods find use inpromoting blood clotting at a hemorrhage site under conditions ofcoagulopathy. By “coagulopathy” is meant a condition where clotformation in a subject is impaired, such as a condition where thesubject's coagulation cascade is impaired. Coagulopathy may include oneor more of a subset of conditions, such as dilution, hypothermia andacidosis. As such, the subject hemostatic compositions, devices andmethods find use in promoting blood clotting at a hemorrhage site when asubject's coagulation cascade is impaired, such as under one or morecoagulopathy conditions, such as dilution, hypothermia and acidosis.

For example, the subject hemostatic compositions, devices and methodsfind use in promoting blood clotting at a hemorrhage site under adilution condition, e.g., the subject hemostatic compositions, devicesand methods are hemostatically effective even when the concentration ofprocoagulant factors at the hemorrhage site is insufficient to have asignificant hemostatic effect, as may occur as the result of traumaand/or loss of blood. Similarly, in certain embodiments, the subjecthemostatic compositions, devices and methods find use in promoting bloodclotting at a hemorrhage site under a condition of hypothermia, e.g.,the subject hemostatic compositions, devices and methods arehemostatically effective even when the subject's body temperature dropsbelow 37° C., as may occur as the result of trauma and/or loss of blood.In addition, in some embodiments, the subject hemostatic compositions,devices and methods find use in promoting blood clotting at a hemorrhagesite under a condition of acidosis, e.g., the subject hemostaticcompositions, devices and methods are hemostatically effective even whenthe pH of blood is below its typical value of pH 7.4, as may occur asthe result of trauma. In certain embodiments, the subject hemostaticcompositions, devices and methods find use in promoting blood clottingat a hemorrhage site under one, or a combination of two or more,coagulopathy conditions.

EXAMPLES

The following examples are put forth so as to provide those of ordinaryskill in the art with a complete disclosure and description of how tomake and use the present invention, and are not intended to limit thescope of what the inventors regard as their invention nor are theyintended to represent that the experiments below are all or the onlyexperiments performed. Efforts have been made to ensure accuracy withrespect to numbers used (e.g. amounts, temperature, etc.) but someexperimental errors and deviations should be accounted for. Unlessindicated otherwise, parts are parts by weight, molecular weight isaverage molecular weight, temperature is in degrees Celsius, andpressure is at or near atmospheric.

Example 1

Materials

Ethanol (99%), tetraorthoxilicate (TEOS), ammonia NH₄OH (28%),(3-aminopropyl)triethoxysilane (APTES) were supplied by Sigma Aldrich.Deionized water was obtained using a Milli-Q water purification system.Frozen pooled normal plasma (PNP) and Factor XII-deficient plasma werepurchased from George King Biomedical (Overland Park, Kans.) and handledaccording to package inserts. Phospholipid solutions in chloroform werepurchased in Avanti Polar Lipids: L-alpha-phosphatidycholine (PC) andL-alpha-phosphatidylserine (PS). Sodium chloride, potassium chloride,sodium phosphate, dibasic and potassium phosphate—for Phosphate BufferSaline (PBS), were supplied by Sigma Aldrich.

Synthesis of Silica Nanoparticles

Silica nanoparticles (SNP) were synthesized following a modified Stöbermethod. (W. Stober, A. Fink, E. Bohn, Controlled growth of monodispersesilica spheres in the micron size range, Journal of Colloid andInterface Science. 26 (1968) 62-69). For the synthesis of silicananoparticles, tetraethoxysilane (TEOS) and ammonia were added dropwiseand consecutively into 57 mL of ethanol while stirring at 300 rpm atroom temperature. The stirring was continued for 24 h. pH and particlesize was measured after synthesis. The material was recovered bycentrifugation (14 k, 30 min), washed with ethanol to remove ammonia andunreacted TEOS (3 times). After redispersing the material in ethanol bysonication (FS20 Fisher Scientific), the products were dried overnightat 60° C. and once homogenized, calcined at 550° C. during 4 h.Different amounts of TEOS (0.5-4 mL) and ammonia (0.5-4 mL) were used toproduce different particle sizes.

Particles above 10 nm were synthesized following the modified Stobermethod and recovered using centrifugation as described above. Differentnanoparticle sizes were obtained by varying the amounts of TEOS andammonia (NH₄OH). FIG. 1 shows a graph of average particle size (nm) ofthe silica nanoparticles vs. amount of NH₄OH (%) added to the reaction.The average size increased as the amount of NH₄OH added increased. SigmaAldrich supplied Ludox silica nanoparticles for nanoparticles withaverage sizes below 10 nm. Silica nanoparticles below 50 nm wereisolated by ultrafiltration and ultracentrifugation to provide a stockfor coagulation and functionalization experiments. FIG. 2 shows a graphof the yield (%) of silica nanoparticles vs. amount of NH₄OH (%) addedto the reaction. The yield increased significantly for NH₄OH of 4% ormore. Syntheses below 4% NH₄OH produced a yield below 40%. In someinstances, a low amount of ammonia may slow catalysis of the TEOShydrolysis reaction.

Preparation of Polyphosphate Polymer

Medium chain polyphosphate (30-130mer, “P70” was purified fromcommercially available industrial source phosphate glass (“P70”, BKGuilini GMBh, Germany). Long chain polyphosphate (“P700”), wassolubilized from phosphate glass, practical grade, water insoluble(Sigma Aldrich) in 250 mM LiCl+50 mM LiOH, pH 10.5 at 100° C. Thematerial was then precipitated with 50 mM NaCl in 2 times the volume ofisopropanol, and resuspended in double distilled H₂O.

Two different sizes of polyphosphate polymer were used: P70, with anaverage chain length of 70 monomers, and P700, with a size range between200 and 1300 monomers and a peak concentration at about 700 monomers.

Synthesis Silica-Polyphosphate Nanoparticles

The synthesized polyphosphate was used to functionalize the silicananoparticles. The silica nanoparticles were dispersed by sonication inMilli-Q water and placed at 30° C. Then polyphosphate was added undervigorous stirring. The stirring was continued for 12 h. Thefunctionalized nanoparticles were recovered after two centrifugationsteps (14 k, 30 min), washing with ethanol, redispersing by sonicationin ethanol and finally drying overnight at 60° C. Successfulfunctionalization of the nanoparticles was identified using a dynamiclight scattering (DLS) instrument.

Characterization of the Nanoparticles

Zeta Potential and Particle Size Determination

Zeta potential and particle size were measured by laser diffractometryusing a Zetasizer Nano ZS instrument (ZEN 3600, Malvern Instruments) at20° C. with an incident wavelength of 633 nm and 173° backscatteringangle. Zeta potential was measured in water at different pH and in PBSbuffer (137 mM NaCl, 2.7 mM KCl, 12 mM phosphate). Disposable cells werecleaned with ethanol and water prior to sample loading. Particle sizewas measured just after the particles were synthesized (with ethanol asa solvent) and after the calcination step, redispersed by sonication inwater at 1 mg/mL. Disposable cells were cleaned with each respectivesolvent before sample loading.

Zeta potential tests showed that SNPs had a negative charge in simulatedbody fluid, which may facilitate activation of the intrinsic pathway byactivating Factor XII. Zeta potential exhibited no systematic change incoagulation with respect to size or pH.

FIG. 97 shows a graph of clotting times for various SNPs (e.g., SNP,SNP+APTES, SNP+linker, SNP+APTES+linker; SNP+peptide, SNP+APTES+peptide,SNP+PEG, and SNP+APTES+PEG; see examples below for a description of thelinker and peptide). Zeta potentials for each type of particle are alsoindicated on the graph. SNP+PEG and SNP+APTES+PEG had zeta potentialsthat were less negative than other particles, which corresponded tolonger clotting times, R. The relationship between zeta potential andclotting time for SNP with and without 3-aminopropyl-triethoxysilane(APTES) is shown in FIG. 98.

FIG. 99 shows a graph of zeta potential vs. the ratio of APTES/TEOS usedin the synthesis of SNPs. A more positive zeta potential indicated thepresence of amino groups on the particle surface. FIG. 100 shows a graphof zeta potential vs. the ratio of APTES/TEOS for calcined and notcalcined SNPs. With calcination, the amino group decomposed and the zetapotential was more negative. FIG. 101 shows a graph of clotting time vs.zeta potential for calcined and not calcined SNPs. A negative zetapotential produced a lower clotting time.

Morphology and Structure of the Particles

The morphology, structure and particle size of the nanoparticles weredetermined via transmission electron microscopy (TEM). TEM micrographswere obtained on a FEI Tecnai G2 Sphera electron microscope with anaccelerating voltage of 200 kV.

P70 directly adsorbed to silica was found to only slightly increase theparticle size (by several nm). FIG. 4 shows TEM micrographs of silicananoparticles of 55 nm average size.

Quantification of the Polyphosphate

The polyphosphate content on the particles was quantified by hydrolysisto monophosphate using calf intestinal alkaline phosphatase, followed byphosphate analysis using a malachite green assay.

Determination of Clotting Activity

The clotting activity was determined by two different methods: standardcoagulometry and rotational thromboelastometry (TEG) in athrombelastograph (TEG® 5000, Haemonetics). These tests measure severalparameters that are relevant to coagulation, such as initial time forclot formation (R, min), rate of clot formation (α, deg), time untilclot reaches 20 mm (K, min) and clot strength or maximum amplitude (MA,mm). For the tests, the particles were dispersed in HBS containingphospholipid vesicles and sonicated. The phospholipids were 80%phosphatidycholine (PC) and 20% phosphatidylserine (PS) and wereprepared by sonication from the commercial solutions in chloroform. Thesubsequent dilutions were made by diluting the stock dispersion in thissame solvent.

For the coagulometry tests, 50 μL of the particles were placed into apre-warmed coagulometer cuvette followed by 50 μL of pooled normalplasma (PNP). After incubating for 33 minutes at 37° C., to activate thecontact pathway and allow the mixture to reach the proper temperature,50 μL of pre-warmed 25 mM CaCl2 was added into the cuvette. The resultswere the average values of duplicate tests.

In the TEG tests, first 340 μL of pooled normal plasma (PNP) and 10 μLof the clotting agent were added in the TEG cup and incubated at 37° C.After 3 minutes, 20 μL of 0.2 M CaCl₂) was added to the cup and the testwas started immediately after. The results shown were the average valueof, typically, 4 to 6 replicates. Concentration- and size-dependentanalyses were done.

Results and Discussion

Experiments were performed with silica nanoparticles (SNPs) andpolyphosphate-functionalized silica nanoparticles (SNP-P70) to measurethe effect of the silica particles' size and concentration oncoagulation. Clotting experiments compared the silica particles ateither a fixed concentration of 0.68 mg/mL (25 mg/mL stock solution) orat a fixed size of 55 nm to determine high activity range boundaries.Each particle formed an initial clot (R) between 3 and 5 min. Thethreshold for minimum R value occurred at a particle size of ˜30 nm.Experiments in which particles below 20 nm were synthesized exhibited abimodal size distribution when measured using DLS, which may beattributed to an amount of ammonia that was too low for the catalysis ofthe TEOS hydrolysis reaction.

TEG experiments were performed to determine clotting time, R, vs.concentration (mg/mL) of silica nanoparticles (SNP) and silicananoparticles functionalized with polyphosphate polymer (SNP-P70) (70monomer chain length) at 37° C. and 10.8 mM Ca2+. As shown in FIG. 3,the concentration dependence of R for SNP and SNP-P70 was examined. P70was a polyphosphate chain that was approximately 70 monomers in length.At low particle concentrations, the R value was relatively high (e.g.,clotting time was long). As the particle concentration increased, Rdecreased until a minimum R value was obtained. For bare (i.e.,unfunctionalized) silica, the minimum R value occurred at 0.54 mg/ml.SNP-P70 reached a minimum R value at a concentration of 0.27 mg/ml, halfthat of bare SNP. SNP-P70 also improved clotting time when compared toP70 added directly to plasma.

TEG experiments were performed to determine clotting time, R, forSNP-P70 and lipidated tissue factor (LTF), a protein initiator of theextrinsic pathway, at various dilutions of pooled normal plasma (PNP) at37° C. and 10.8 mM Ca2⁺. The concentration of LTF used was 0.5 ng/mL andthe concentration of SNP-P70 used was 0.27 mg/mL. As shown in FIG. 5,when compared with LTF, SNP-P70 induced rapid coagulation even underconditions of hemodilution.

Experiments were performed to determine the mechanism by which P70-boundnanoparticles induce clotting by determining clotting times using FXIIdeficient plasma (FIGS. 6 and 7). As they activate clotting through FXIIactivation and the intrinsic pathway, the bare nanoparticles cold notinduce clotting. With the intrinsic pathway blocked, coagulation onlyoccurred through the addition of tissue factor (TF) and the extrinsicpathway. Since P70 accelerated coagulation through FXa, a combination ofTF and P70-bound silica improved clotting. Various mixtures of TF andnanoparticles were tested. The two lowest clotting times (R) occurred asa result of either 1 ng/mL TF or 0.5 ng/mL TF mixed with 0.676 mg/mLSNP-P70 (FIG. 6). Although the two conditions shared a similar clottingtime, the P70-bound silica rapidly accelerated clot growth as shown bythe significantly larger coagulation index (CI) score (FIG. 7). TheP70-bound silica also exhibited the best reproducibility of all theconditions, which may facilitate a reduction in adverse side-effects.The tissue factor formed a small clot upon addition to plasma, but theclot grew at a slow rate. These tests showed that the P70 boundparticles increased clotting through mediating FXa and thrombin, whichmay facilitate treating hemorrhage.

Experiments were performed to determine clotting time, R, for variousdifferent polyphosphate to SNP ratios. Polyphosphate that included about700 monomer polyphosphate (P700) was used in the experiments.Polyphosphate with a size range above 500mers was shown to acceleratethe contact or intrinsic pathway by activating FXII. The P700 wasattached to the SNP using the same methods described above. Fourdifferent ratios of P700:SNP were tested—0.2, 0.4, 0.6, and 1. Similarto P70, clotting assays showed that clot time decreased with a ratio ofP700:SNP above 0.5. As shown in FIG. 8, a 1:1 ratio of P700:SNPminimized clot time.

Experiments were performed to determine the effect the amount ofpolyphosphate in the functionalized SNP had on coagulation. 200-mgsamples of SNP, SNP-P70, and SNP-P700 nanoparticles were tested forpolyphosphate quantification and coagulation tests. These tests showedthat SNP-P70 particles with a concentration of 25 nmol PO₄/mg SNP(quantified by hydrolysis) exhibited higher procoagulant activity thanSNP-P70 particles with a higher nmol PO₄/mg SNP concentration.

In addition to TEG, the coagulation threshold response was also observedusing a thrombin-specific blue coumarin dye. These experiments used amethod developed by the Ismagilov group (Kastrup, C J, Shen, F, Runyon,M K, et al. (2007). Characterization of the threshold response ofinitiation of blood clotting to stimulus patch size. BiophysicalJournal, 93(8), 2969-77). A small concentration of dye was added torecalcified plasma. As clotting progressed and thrombin was produced,the thrombin cleaved the coumarin dye which caused the solution tofluoresce. Signified by rapid fluorescence, the thrombin burst quicklyled to clot formation. A fluorescence microscope captured thequalitative change as shown in FIG. 9.

Thrombin generation was also monitored using a plate reader. By readingfluorescence every 10 seconds, the thrombin burst was identified. Asclotting occurred near the rapid rise section of the thrombin burst, theclot time was determined from the fluorescence data plot. FIG. 10 showsa graph of fluorescence intensity (a.u.) vs. time for variousconcentrations of SNP and SNP-P70 (see FIG. 10A), and a graph of clottime (half-time, s) vs. concentration (mg/mL) for SNP and SNP-P70 (seeFIG. 10B).

Experiments were performed to determine hemostatic activity at variouscoagulopathy conditions, such as dilution, hypothermia and acidosis. Adilution condition was tested using a phosphate buffered solution (PBS).Hypothermia was tested by incubating plasma below the usual 37° C.,which created a hypothermic condition. Acidosis was tested using adilute phosphoric acid solution to acidify the plasma below a pH of 7.1.The experiments utilized a set concentration of lipidated tissue factor(LTF)—0.5 ng/ml for TEG tests, 0.185 ng/ml for fluorescence dye tests—toensure timely initiation of the coagulation cascade through theextrinsic pathway and the body's main response to vessel injury. TheSNP-P70 was tested at 0.25 mg/ml without LTF to compare its ability toform clots.

Using TEG and dye fluorescence, a dilution baseline was established.SNP-P70 was added at the threshold concentration (i.e., concentrationthat resulted in a minimum clotting time, R) of 0.25 mg/ml identified inthe TEG experiments above. As shown in FIG. 11A, SNP-P70 loweredclotting time in diluted samples. FIG. 11B shows a graph of clot size,MA, (mm) vs. % of pooled normal plasma (PNP). Results of the dyefluorescence experiments at various dilution conditions are shown inFIGS. 12(a) and 12(b). FIG. 12A shows a graph of fluorescence vs. time(sec) for thrombin generation times from 100% plasma to 25% plasma(i.e., 100% plasma is 100% plasma and 0% dilutant) with no SNP-P70added. FIG. 12B shows a graph of fluorescence vs. time (sec) forthrombin generation times at various dilution conditions for sampleswith SNP-P70 added. As shown in FIG. 12B, the addition of SNP-P70generated thrombin quickly even under plasma dilution conditions.

Hypothermia occurs when the body temperature drops below 37° C. The dropin temperature may lead to a decreased rate in the kinetics of many ofthe coagulation factors, such as formation of the tissue factor-FVIIa(TF-FVIIa) complex during the initiation phase of coagulation. FIG. 13Ashows a graph of clotting time, R, (min) vs. temperature (° C.) forexperiments to determine hemostatic activity of SNP-P70 underhypothermic conditions. FIG. 13B shows a graph of coagulation index (CI)vs. temperature (° C.) for SNP-P70 under hypothermic conditions. Theaddition of SNP-P70 to hypothermic plasma resulted in improvedcoagulation across all TEG parameters, including a decrease in clottingtime and an increase in coagulation index. The coagulation index (CI)showed that SNP-P70 had significant procoagulant activity. Thecoagulation index (CI) combines all four TEG facets—R, K, alpha, andMA—into a single value; the more positive the CI, the stronger theprocoagulant.

The experiments described above show that SNP-P70 has significantlygreater hemostatic activity than bare SNP and LTF in lowering clot timeswhile forming strong clots. Experiments on FXII deficient plasma showedthat SNP-P70 initiated clotting through the FXa coagulation pathway.SNP-P70 also decreased clot time and quickened thrombin generation undercoagulopathic conditions, such as dilution and hypothermia.

PEGylated Nanoparticles

Experimental Protocols

Functionalization of SNP with APTES

0.5 g of SNP and 50 Ml ethanol were added to a flask and sonicated. 1 μLof APTES was added while stirring vigorously. The mixture was stirred 24hours at RT. After 24 hours, the mixture was put in centrifuge tubes andspun for 30 min at 14 k. Supernatant was discarded, ethanol was addedand the mixture was sonicated. The mixture was centrifuged for 30 min at14 k. Supernatant was discarded, ethanol was added and the mixture wassonicated. The resulting SNP-APTES was dried overnight at 60° C.

PEGylation of SNP to Produce SNP-APTES-PEG-OCH₃

12.5 mg of SNP-APTES was prepared in 250 μL 1 mM NaOH (50 mg/mL). 2 mgof NHS-PEG-OCH₃ was prepared in 25 μL DMSO (2 kDa, 5 kDa, 20 kDa). 25 μLPEG-solution per 250 μL SNP-APTES was added to the SNP-APTES. Themixture was sonicated and incubated 15 min at RT. The mixture wascentrifuged 2× for 5 min at 3.5 k, and cleaned with DI. The volume wasbrought to 250 μL, and the mixture was sonicated.

Adding Linking Group to SNP-APTES

Four different linkers were used.

Linker MW (g/mol) SPDP-PEG8-NHS 735.87 SPDP-PEG16-NHS 1087.30SPDP-PEG2k-NHS 2000 SPDP-NHS 312

50 mg/mL of the SNP-APTES particles were dispersed in 10 mM NaOH (e.g.,25 mg in 495 μL DI and 5 μL 0.1 M NaOH). The mixture was sonicated. 5 μLof the linker in DMSO (10 mM) was added per 500 μL of SNP-APTES, pH 7-8(100 μM final linker). The mixture was sonicated. The mixture wasincubated 30 min to 2 hours at RT. The mixture was centrifuged 2× for 10min at 6 k, and cleaned with DI, pH 5-8. The volume was brought to 500μL with Mllli-Q water.

Adding Peptide to SNP-APTES-Linker

The following peptides were used.

Long  Short  name name Use MW Ac- C- This peptide included:  1232.34CGGIEGRGG IE-GK a Cys, to attach to the SGG

G-NH2 (CG- OPSS linker; an IEGR  14) sequence for beingrecognized by FXa; and  a Lys, where the PEG was attached. Ac- C-This peptide included  1631.78 CGGIEGRGG IE-FK a Cys for binding to 

(FAM)GGKG- (CG- the linker; an IEGR  NH2 14) sequence for cleavage;  a fluorescein dye (FAM) used to monitor cleav- age; and a Lys for NHS-PEG attachment.  The fluorescein (FAM) was to the right sideof the cleavage site, which resulted in fluorescein in the supernatant after   cleavage by FXa. FAM-x- CF- This peptide included a 1661.79 CGGIEGRGG IE-GK Cys for binding to the SGG

G-NH2 (CG- linker; an IEGR se- 14) quence for cleavage;  a dye used to monitor cleavage; and a Lys for NHS-PEG attach-ment. The fluorescein  (FAM) was to the left side of the cleavagesite, which resulted in fluorescein remaining on the particle aftercleavage by FXa. FAM-x CF- This peptide included a  1661.79 CGGERGIGGErsc- Cys for binding to the SGGKG-NH2 GK linker; a dye used to (CG-monitor cleavage; and a  14) Lys for NHS-PEG attach-ment. The peptide does  not include the IEGR sequence necessaryfor cleavage by FXa.

Peptide solutions were prepared in Milli-Q water, e.g. 0.75 mM.Concentrations of peptide used were: (a) 1.1 mg/mL C-IE-GK, (b) 2 mg/mLC-IE-FK, (c) 2.1 mg/mL CF-IE-GK, and (d) 2.1 mg/mL CF-Ersc-GK. 50 μL ofthe peptide solution was added to 500 μL particle solution (50 mg/mLparticles). The mixture was incubated for 10 min at RT, and thencentrifuged 10 min at 6 k. Supernatant was removed and reaction productwas washed with DI, and the volume was brought to 500 μL. Spinning andwashing were repeated, and the volume was brought to 500 μL with Milli-Qwater.

Functionalization of SNP Through SPDP

Nanoparticles were prepared with the following structure:SNP-APTES-SPDP-cysPep-K-PEG-OCH₃.

SNP was prepared by adding dropwise 7.6 mL of TEOS into a stirredsolution 280 mL of ethanol. 11.4 mL NH₄OH (28%) was added dropwise andthe mixture was stirred for 24 hours. The mixture was centrifuged 3× for30 min at 13 k, and washed with ethanol. SNPs were dried overnight at60° C. SNPs were calcined at 550° C. for 4 hours.

SNP-APTES was prepared by adding 0.5 g of SNP in 50 mL ethanol andsonicating. APTES was added while stirring vigorously. The mixture wasstirred for 24 hours, and then centrifuged 2× for 30 min at 13 k, andcleaned with ethanol. The SNP-APTES was dried at 60° C. overnight andthen ground with a mortar.

Succinimidyl 3-(2-pyridyldithio)propionate (SPDP) was added as follows.50 mg/mL of SNP-APTES was dispersed in 10 mM NaOH (e.g., 25 mg in 495 μLDI and 5 μL 0.1 M NaOH) and sonicated. 3.1 mg/mL SPDP in DMSO (MW 312)(10 mM stock) (e.g., 1 mg in 320 mL) was prepared. 5 μL SPDP per 500 μLof SNP-APTES, pH 7-8 (100 μM final SPDP) was added and the mixture wassonicated. The mixture was incubated 30 min to 2 hours at RT. Themixture was centrifuged 2× for 10 min at 6 k, and cleaned with DI, pH5-8. The volume was brought to 500 μL.

A peptide was added as follows. 50 μL of 2 mg/mL cys-peptide-K (e.g.,biotin-x-CDGSRPARSGR″SAGGKDA-OH) was added to the above solution andincubated 10 min at RT. The mixture was centrifuged 2× for 5 min at 6 k,and cleaned with DI. The volume was brought to 500 μL.

SNP-APTES-SPDP-cysPep-K was PEGylated as follows. 4 mg of NHS-PEG-OCH3in 50 μL DMSO (2 k PEG or larger) was prepared. 50 μL PEG solution per500 μL SNP-APTES-SPDP-cysPep-K was added and the mixture was incubate 10min at RT. The mixture was centrifuged 2× for 10 min at 6 k, and cleanedwith DI. The volume was brought to 500 μL.

The resulting structure was SNP-APTES-SPDP-cysPep-K-PEG-OCH3. The PEGprotected nanoparticle were non-coagulating.

The cleavable peptide linker was cleaved by adding an enzyme as follows.To 50 μL of SNP-APTES-SPDP-cysPep-K-PEG-OCH₃ was added 50 μL of uPAenzyme (urokinase plasminogen activator) or trypsin, and the mixture wassonicated, 10-60 min (e.g., 30 min) at 37° C. The mixture wascentrifuged, washed and volume adjusted to 50 μL with DI.

The structure was now SNP-APTES-SPDP-cysPepR-OH, and was hemostaticallyactive.

SNP-APTES Conversion to PEG-OPSS and Coupling to Biomolecule

Reactions:SNP—NH₂+NHS-PEG-OPSS→SNP-linker-PEG-OPSS

OPSS is S—S-Pyridyl, which reacts with thiols to form a disulfideproduct:R₁—S—S-Pyr+HS-R₂→R₁—S—S—R₂+S=Pyr

where R₁ is the nanoparticle, R₂ is the biomolecule

SNP-APTES 0.1 g (220 nm diameter) was dispersed in 5 mL DI withsonication. NHS-PEG-OPSS 5 kDa, 10 mg, was dissolved in DMSO (0.5 mL).The PEG solution was added to the SNP-APTES solution and the mixture wassonicated. pH was adjusted to pH 7 with HEPES buffer. The mixture wassonicated and incubated 1 hour. The mixture was centrifuged and cleaned2-3× with washing buffer. The volume was brought to 5 mL. The couplingreaction to a thiol-containing biomolecule was performed by addingtogether 200 μL SNP-linker-PEG-OPSS, 200 μL buffer (1M Hepes), and 20 μL1 mg/ml peptide in 1M Hepes. The mixture was incubated at roomtemperature for 1 hour, cleaned 3 times, and stored at 4° C.

Results and Discussion

PEGylated nanoparticles were prepared that included a cleavable peptidelinking group with an IEGR sequence that connected the nanoparticle tothe PEG (FIG. 14). Activated Factor X (FXa) cleaved the peptide at theIEGR sequence, removing the PEG and leaving the activated SNP.

FIG. 15 shows a graph of clotting time, R, vs. 3-aminopropyltriethoxysilane (APTES) to SNP ratio, according to embodiments of thepresent disclosure. FIG. 16 shows a graph of clotting time, R, forunfunctionalized SNP and various functionalized SNPs (Pep: peptide;SPDP: succinimidyl 3-(2-pyridyldithio)propionate; PEG used was 2 kDa),according to embodiments of the present disclosure.

When bound to the nanoparticle surface, cross-linkers such as3-aminopropyl triethoxysilane (APTES) reduced the active surface forcoagulation (FIGS. 15 and 16). The ratio of APTES to silica wasdecreased to obtain a PEG-linker-APTES-silica SNP that would retain adual nature—inert in healthy blood vessels while converting toprocoagulant when activated by a linker-specific protease. Whenfunctionalized solely with APTES, at low coverage, the SNP retained itsprocoagulant nature. When PEG attached to these nanoparticles via theAPTES, the SNP became protected. Coupling PEG (2 kDa or more, e.g., 5kDa) increased clotting times back to that of normal recalcified plasma.Removing PEG activated the procoagulant activity of the SNP.

Example 2

Particle Design and Tests

Experiments were performed to conjugate polyP onto the surfaces oforganic and inorganic particles to investigate the effects of particlesurface properties (i.e. surface charges and ligands) and particlesizes. Hybrid particles were generated with thermal sensitive orchemically responding polymers and polyP at the surface. Under theswitch conditions (such as, lower temperature or over expressedchemicals), the polymer brushes were extended or folded to either shieldor expose the surface ligands such as polyP.

In certain embodiments, polyP activates and accelerates the clottingcascade. In some instances, steps in clotting are enhanced by polyP.Size dependence of polyP's procoagulant activities showed that shorterpolyP polymers accelerated the activation of factors V and XI, whilelonger polyP polymers initiated clotting via the contact pathway (FIG.17). In some cases, the specific procoagulant activity ofpolyP-containing nanoparticles may be tailored by varying the polyPpolymer lengths used, as well as by controlling the amount of polyP perparticle. The polyP particles may have the capacity to induce clottingin a controlled and directed manner, compared to free polyP. Withoutbeing limited to any particular theory, in some instances, polyPparticles may interact with blood plasma and cause a series of events,including the adsorption of albumin, IgG and fibrinogen, plateletadhesion and activation, and thrombosis. PolyP may shorten the clottingtime, depending on the concentration, size and surface properties of theparticles.

Experiments were performed for covalently attaching polyP to primaryamines, which facilitated polyP-nanoparticle assembly. This reactionused the zero-length cross-linking reagent, EDAC(1-ethyl-3-[3-dimethylamino)propyl]carbodiimide), to promote theformation of stable phosphoramidate linkages between primary amines andthe terminal phosphates of polyP. Other functional groups may be used atthe termini of polyP, in order to broaden the types of couplingreactions that may be used. Nearly 80% end labeling was achieved usingpolyamines such as spermine and spermidine. The reaction productcontained primary amines attached to the ends of the polyP polymers,which reacted with a wide variety of derivatizing reagents that targetprimary amines. Free sulfhydryls groups may also be introduced onto thetermini of the labeled polyP polymers, in order to usesulfhydryl-labeling chemistries.

Multiple terminal amine surface groups may also be used to conjugate acontrolled number of polyP with these surface amines. G4Poly(amidoamine) (PAMAM) dendrimers associated tightly with polyP and may serve asa platform for assembling polyP-containing nanoparticles. PolyPconjugation to three types of particles (e.g., G4Poly(amido amine)(PAMAM) dendrimers, amino polystyrene, and amine ligands bound to goldnanoparticles) were investigated to verify three hypothesis: (1) plasmaclotting kinetics and mechanism was affected by the size (or curvature)of the particles and an optimized condition could be selected; (2) thechoice of the biocompatible core material would not have significanteffects on the plasma clotting kinetics or mechanism; and (3) thefunctionalities of the particles was determined by the surfaceproperties (e.g., neutral vs. charged and the chain length of polyPs).

In certain embodiments, the total number of polyP chains affectedclotting of plasma. In some cases, the mechanism and time to clotchanged with free chains of polyP. Three control groups were selected tocompare with the particles-polyP conjugates: (1) free polyP with thesame molecular weight at the same concentration; (2) linear polyP withthe molecular weight equivalent to the summation of polyP the molecularweight attached on a single particle (e.g., polyP molecular weight timesthe conjugation number); and (3) particles without polyP.

Dendrimer-polyP Conjugation

PolyP (45-mer) was conjugated to the G4 PAMAM dendrimer, which had 64primary amines on the surface. The zero-length cross linking reagent,EDAC was used to couple primary amines to phosphates via phosphoramidatelinkages. The separation of free polyP and dendrimer-polyP conjugate wasdone by employing size exclusive columns. The plasma clotting efficiencywas tested by using a viscosity based coagulometer.

To find out the optimized conditions for conjugation, variousconditions, such as the temperature, pH and reaction time were tested.The fluorescamine assay was used to test the amount of the unreactedprimary amines on dendrimer, which indicated the conjugation efficiency.

The conjugation efficiency under various conditions was tested and shownin FIG. 18. The reactions were more efficient at low pH conditions. Theamine concentration before the reaction was about 3400 nM. In somecases, there was a higher amine concentration after reaction as comparedto the control, which was due to the degradation of the dendrimer(discussed below). The optimized condition was selected as 4 hours at37° C. and pH 4, after which >80% of the primary amine on dendrimer hadreacted with polyP.

Dendrimer and polyP Stability

The stability of polyP at 37° C. after 24 hours was tested as a functionof pH (FIG. 19). Compared to the sample at pH 7.4, there was no increaseof free phosphate, which indicated little degradation. Therefore, polyPwas stable for the first 24 hours at 37° C. and as low as pH 2. Thestability of dendrimer at various conditions was also tested. Below pH 4and above 32° C., more than 25% dendrimer degraded within 4 hours. At20° C. and pH 4, the dendrimer was stable for the first 4 hours andabout 10% degradation happened at 24 hours. Separation Econo-Pac 10DGColumns were first used to separate the free polyP and dendrimer-polyPconjugates. Recovery of dendrimer was highly depend on the runningphase. When purified water was used as the running phase, as shown inFIG. 20, the dendrimer eluted in the 9th fraction but recovery ofdendrimer was only about 5%. In some cases, the dendrimer may have beentrapped in the column because of ionic interactions. Therefore, in laterexperiments, buffers with at least 20 mM salt concentration were used toeliminate the effect of ionic interactions between the gel and thesolute. As an example, with 25 mM borate acid buffer at pH 9, dendrimereluted at the 4th fraction and recovery rate was above 85% (FIG. 21).Dendrimer-polyP conjugate was then separated on the column (FIGS. 22 and23). The dendrimers eluted at the 6th fraction, while the peak of polyPwas from the 5th fraction to the 7th fraction. Therefore, separation offree polyP from the conjugate through the Econo-Pac 10 DG Column was notachieved.

Size exclusion columns packed with Bio-Gel® P-10 gel were then used forthe separation of conjugated polyP from the un-reacted polyP. Bio-Gel®P-10 Gel with a molecular weight (MW) fractionation range from1,500-20,000 was selected, which was suitable to separate thepolyP-dendrimer conjugation (MW_(>)20,000) from the un-reacted ones(MW_(<)13,700) The dendrimer eluted at the 10th fraction and the polyPcame out at the 9th fraction (FIGS. 24 and 25), which was deemedinsufficient separation.

Another separation method tested was with “glass milk”, which consistedof silica particles in aqueous solution. 1 μL of glass milk was added to500 μL of dendrimer-polyP reaction. The glass milk and reaction was thenmixed for 30 minutes with occasional vortexing. After mixing, thesolution was then centrifuged for 10 minutes at 3,500 RPM. The purifiedsupernatant was collected and the malachite green assay (whichquantified phosphate following acid digestion of polyP) was performed toquantify polyP concentration against the same reaction that had notundergone glass milk purification. FIG. 26 shows a decrease in phosphateconcentration of over 90% before and after the glass milk separation.

The glass milk assay was performed again and both the malachite greenand fluorescamine assays were performed to ensure that only free polyPwas removed by the glass milk and that the dendrimer remained insolution. The results in FIG. 27 indicated less efficient separation ofpolyP than the previous experiment as well as a similar decrease inprimary amine and polyP concentrations before and after the glass milkassay. The concentration of primary amine in the control reactionincreased from the initial amount expected before reaction, which mayhave been due to degradation of the reacted dendrimer over time.

Clotting Tests

Plasma clotting times were tested by using a coagulometer. The samplewas dendrimer-polyP conjugate which reacted at 37° C., pH 4 for 24hours. The clotting time for this sample was 143.8 seconds (FIG. 28).

Polystyrene (PS)-polyP Conjugation

Experiments were performed for making a polystyrene (PS)-polyPconjugation. The general procedure for making the PS-polyP conjugationwas as follows:

-   -   1-2 mL reactions were setup using conditions previously        described in amine polyP reactions.    -   250 mM of 45-mer polyP was added from an aqueous bulk solution        made from sodium phosphate glass purchased from Sigma Aldrich.    -   100 mM pH 4 MES buffer was added to the reaction.    -   300 mM of EDAC was added to the reaction to activate the        reaction between polyP and primary amine.    -   The amount of primary amine on the surface of the PS particle        was characterized using fluorescamine assay. 0.21 mM of primary        amine was added to the solution. This was approximately 5 times        less than the concentration of polyP chains.    -   The reaction was brought up to volume with DI water.    -   The reaction was allowed to proceed for up to 24 hours with        vigorous stirring with the concentrations of primary amine        consumed tested at various time points.

Polystyrene beads (diameter of 50 nm) with primary amine as the surfacefunctional group were used to conjugate polyP. The reaction conditionwas 20° C. and pH 4. After 24 hours, more than 60% of the primary aminewas reacted with polyP (FIG. 29).

The stability of PS beads was tested. As shown in FIG. 30, the amount ofamine was stable at 20° C., but increased at 37° C. In some cases, thismay be due to that at higher temperature and low pH, amine groups buriedinside the particles could be exposed on the surface, which may resultin an underestimation of the reaction efficiency.

Gold Nanoparticle-polyP Conjugation

Experiments were performed for making a gold nanoparticle-polyPconjugation. The general procedure for making the goldnanoparticle-polyP conjugation is shown below.

General Reaction Mechanism:

A. A bulk solution of the thiol-amine ligands of 10.2 mM was made inwater and stored at 4° C.

B. PolyP and amine ligands were reacted as previously described with aratio of 5:1 excess of polyP. Reactions were performed in pH 4 MESBuffer at 37° C. and at ambient temperature (25° C.).

C. The amount of reacted ligand was determined using the fluorescamineassay.

D. Thiol-reacted ligands were bound to 5 nm citrate-coated goldnanoparticles by adding a 20× dilution of the ligand reaction with anexcess of 50:1 thiol ligand to gold nanoparticles. About 12-16 ligandswere bound to each nanoparticle based on studies that found that 130ligands were normally bound to 15 nm gold nanoparticles.

E. The mixture was periodically vortexed and continuously mixed for 8hours.

F. The gold nanoparticle mixture was centrifuged at 13,500 RPM for 20minutes to remove excess polyP and unbound ligands.

G. The supernatant was removed and the pellet was washed and resuspendedwith 450 μL DI water.

H. The centrifuging and washing was repeated twice.

I. UV spectroscopy, malachite green assays, and fluorescamine assayswere performed to quantify the number of polyP chains bound the surfaceof the gold nanoparticle.

A preliminary study of the reaction of amine ligands with polyP at 37°C. demonstrated that primary amine levels decreased around 75% after 24hours of reaction, indicating a 75% reaction completion of amine withpolyP. However, the level of primary amine increased to approximatelyhalf of its control concentration after 48 hours which suggested thatbonds may have hydrolyzed. The concentration of amine in the control at37° C. did not substantially change, which may indicate that thedifference in the reaction amine concentration cannot be explained bythe assay itself (FIG. 31). A calibration curve of primary amineconcentration at excitation and emission wavelengths of 410 and 480 nm,respectively, is shown in FIG. 32.

The thiol-amine ligand reaction with polyP at room temperature was shownto have been completed between 75% to 80% of the ligands in solution.FIG. 33 details the results of the reaction optimization. Theconcentrations in the above reaction scheme except with a 0.42 mMconcentration of amine bound ligand, yielded approximately a 5:1 ratioof polyP chains to amine. Comparing the reactions performed at 37° C.with the ones performed at room temperature indicated that the bonds ofthe amine-polyP hydrolyzed at 37° C. over time. Therefore, bothreactions had similar efficiencies and after 72 hours at roomtemperature more than 75% amine was consumed.

Different ratios of polyP to amine were tested, which may affect thefinal ratios of amine-thiol ligand to the polyP-thiol ligand. Thecompleted reactions mixed with gold nanoparticles were pelleted aftercentrifugation (FIG. 34).

Modification of the gold nanoparticles may also be performed, such as,but not limited to: (1) producing various particle sizes; (2) modifyingwith other reaction mechanisms; and (3) separation and purification. Todemonstrate that the core material does not substantially affect theclotting kinetics, experiments may be performed to: (1) compare thegold-polyP conjugates with other particles, and (2) crosslink a thinpolymer layer and then dissolve the gold.

Particle Design and Tests

Experiments were performed to design and synthesize solid and porousnanoparticle materials that exhibit biocompatibility and rapid thrombusformation. In certain embodiments, the nanoparticles restricted activityto a local region of above-threshold coagulation activity. Experimentswere performed on two nanoparticles—procoagulant silica and medicalimplant compatible titania. The nanoparticle scaffolds werefunctionalized with a procoagulant compound—thrombin, tissue factor, orpolyP—to form a threshold-switchable particle (TSP) that furtherpromoted clot formation. Thrombin, a protein in the coagulation cascade,has a hydrodynamic radius of roughly 8.4 nm. A porous nanoparticle witha minimum pore size of 10 nm can be loaded thrombin. Characterization ofthe particles included microscopy, zeta potential, dynamic lightscattering, and other tests. Thromboelastography (TEG) plasma clottingexperiments were used to study the procoagulant activity offunctionalized and un-functionalized nanoparticles introduced torecalcified pooled normal plasma (PNP).

Silica Nanoparticle Synthesis—Mesocellular Foam

Experiments were performed to synthesize a porous nanoparticle with adiameter smaller than 200 nm and a pore size greater than 20 nm. Ananoparticle of this size may facilitate a reduction in organ damage,while being able to transport and deliver thrombin and other coagulationfactors.

Experiments were performed to synthesize a mesoporous mesocellular foamwith a 26 nm pore size (MCF-26) and particle diameter below 1 μm.Mesocellular foams (MCF) with pore sizes of 11.2 nm, 24.3 nm, and 30.9nm pore size were created. The foams were characterized using BET.Window size was determined from desorption isotherms using theBroekhoff-de Boer (BdB) method; pore size from the adsorption isothermusing the same BdB method. Particle diameters were measured usingscanning electron microscopy (SEM) imaging. The experiments demonstratedthe ability to precisely define pore sizes in the range desired forenzyme and large biomolecule delivery using a particle size <200 nm,which may be useful for cardiovascular delivery.

A second synthesis procedure was used for the synthesis of flocculatedmesoporous silica (FMS) particles with nanofiber or nanospheremorphology (FMS-nf, FMS-ns). FMS-nf and FMS-ns were chosen to synthesizenanoparticles under 200 nm. Dynamic light scattering indicated aparticle size of 250+/−50 nm. Capping and coagulation experiments werecarried out using FMS silica nanoparticles.

These two procedures used solution sol gel or colloidal silicaprecursors. The silica synthesis methodology was based on thepoly(lactic-co-glycolic acid) (PLGA) method for drug delivery as shownin FIG. 35, panel A, and FIG. 35, panel B. The silica synthesisprocedure used trimethylbenzene (TMB) and NH₄ F used in the MCFsynthesis; and a triblock copolymer, P123, combined with a cationicsurfactant, CTAB, to create a liquid silica precursor. Using thisapproach, silica particles with average nanoparticle diameters of125+/−25 nm were synthesized. The 18.2 nm pore size was sufficient forembedding thrombin.

Nitrogen adsorption/desorption isotherms and pore size distribution forall three mesocellular foams were analyzed. FIG. 36 shows the x-raydiffraction pattern and FIG. 37 shows the scanning electron microscopyimages for MCF-24. FIG. 38 shows a graph of pore size distribution ofmesocellular foams calculated desorption branch by BJH method. FIG. 39shows a graph of pore size distribution of porous silica calculateddesorption branch by BJH method. Finally, Table 1 lists the propertiesfor all three mesocellular foams.

TABLE 1 Textual properties of synthesized mesocellular foams BJH WindowBJH Cell BET Surface Pore MCF Size Size Area Volume Sample (nm) (nm)(m²/g) (cm³/g) MCF-11 11.2 19.3 591.7 1.7 MCF-24 24.3 39.3 321.0 2.4MCF-31 30.9 42.4 222.4 1.6Titania Nanoparticle Synthesis

The use of solid silica and titania nanoparticles as carriers may alsofacilitate a restriction of coagulation activity to a localizedthreshold region. Solid silica nanoparticles with particle diametersbetween 5-100 nm may be synthesized. Capping procedures can be used tobind polyP and coagulation factor proteins to the nanoparticle surface.Solid silica nanoparticles with defined system residence times, polyPand thrombin loadings may facilitate a restriction of their activity toa local region of above-threshold coagulation activity.

Titania nanoparticles were synthesized via a phosphoric acid pathway andcharacterized using SEM and X-ray diffraction. The particle diametersaveraged 225+/−50 nm. Along with the silica FMS, titania particles wereused in functionalization studies.

FIG. 40 shows SEM images of TiO₂ synthesized via the phosphoric acidpathway. The conjoined nature of the separate particles occurred due tosputtering for SEM imaging.

PolyP Capping

Experiments were performed on two polyP capping pathways. The firstpathway utilized the Lewis acid properties of both silica and titania.The process of Lorenz et al., Anal. Biochem., 1994, 216:118-26, wasadapted by replacing zirconia with either silica or titania. Thenegative shift in zeta potential illustrated in FIG. 36 indicated thatpolyP successfully bound to its target.

The second pathway used (3-aminopropyl)-triethoxysilane (APTES) to forma bridge between the nanoparticle and the procoagulant material. Theprimary amine terminus of APTES bound with proteins or EDAC-modifiedpolyP. PolyP bound to amine surface strip wells using EDAC, polyP,APTES-modified silica, and 2-(N-morpholino)ethanesulfonic acid (MES).Zeta potential and Fourier transform infrared (FTIR) spectroscopy showedthat the nanoparticles had been functionalized with APTES. Zetapotential measurements were used to determine that the polyP bound tothe particles. FIG. 41 shows a FT-IR spectrum of unmodified andAPTES-modified titania nanoparticles. C—H, N—H, and Si—O-Si bandsindicated successful attachment of APTES to TiO₂ molecules. FIG. 42shows a graph of zeta potential titration of unmodified and modifiedtitania nanoparticles.

Protein Capping

Experiments were performed for capping solid nanoparticles with thrombinusing the APTES mechanism described above. The mechanism involvedbinding a slowly deprotected thiol on the APTES-nanoparticle scaffold tothe thiol-reactive group on the protein. This pathway may minimizeaggregation of particles and proteins due to a fast reaction rate thatwould result in one particle binding to one protein.

Other active agents can be integrated with the nanoparticles to treatinternal wounds. For example, a tissue factor (TF)-Nanodisc agent can beused to initiate coagulation. In addition, delivering additionalfibrinogen to a wound site can replenish the fibrinogen concentrationand may lead to a stronger clot.

Thromboelastography

Several silica samples—both naked and polyP capped—were tested forprocoagulant activity using plasma in a thromboelastograph (TEG)instrument. The TEG measurement focused on four coagulant parameters: R,time until first clot; K, time from initial clot formation to 20 mm clotdiameter; α, clot formation speed; MA, clot strength. As listed in Table2, these data indicated that the polyP-capped silica decreased the timeand speed of clot formation.

TABLE 2 TEG measurements for controlled pooled normal plasma, FMS-ns,and polyphosphate-modified FMS-ns. Run R(min) K(min) Angle(deg) MA(mm)Control Average 13.40 3.70 55.63 37.77 Control St. Dev. 1.28 0.36 7.758.35 FMS-ns Average 7.98 1.98 63.93 31.25 FMS-ns St. Dev. 0.67 0.9512.19 6.43 FMS-ns-PolyP Average 7.03 1.30 77.63 28.43 FMS-ns-PolyP St.Dev. 0.50 0.46 3.52 2.32Biocompatibility

Experiments were performed to examine the cytotoxicity of MCF-26 onhuman cells. Experiments were performed to test MCF-26 absorption byHUVEC (Human Umbilical Vein Endothelial Cells), HEK-a (Human EmbryonicKidney), HDF-a (Human Dermal Fibroblast), HPTC (Human Renal ProximalTubule), HK-2 (Human Kidney 2), and NIH-3T3 fibroblast cells. Thecytotoxicity studies showed that MCF-26 nanoparticles are not toxic,even at high concentrations. Typically, silica particles have IC50values in the μg/ml concentration range. Even for the highly sensitiveHUVEC cells, MCF-26 IC50 values ranged between 0.7-6.3 mg/ml. Cells didnot readily absorb MCF-26 particles until the concentrations reached themg/ml scale. FIG. 43, left, shows images of the uptake of varioussamples by HUVEC (Human Umbilical Vein Endothelial Cells), with Ag NPconcentration of 10 μg/ml; Kaolin concentration of 10 μg/ml; and MCF-26concentration of 100 μg/ml. FIG. 43, right, shows images of the uptakeof various samples by HDFs, with Ag NP concentration of 20 μg/ml; Kaolinconcentration of 20 μg/ml; and MCF-26 concentration of 100 μg/ml. Table3 shows IC50 (mg/ml) and % viability values of rneural red uptake assayof MCF-26.

TABLE 3 Neural red uptake assay values for MCF-26. Cell Type IC50(mg/ml) % Viability at C_(max) = 7 mg/ml HUVEC 5117 6.3 ± 0.2  50% ±3.4% HUVEC 5025 2.1 ± 0.8 26.6% ± 6.7% HUVEC 3516 0.7 ± 0.0 20.8% ± 2.0%HDF-a (ScienCell) 2.0 ± 0.2 13.4% ± 2.8% HDF-a (PromoCell) 5.6 ± 1.439.5% ± 8.0% HDF-a (ATCC) 5.0 ± 0.7 41.4% ± 3.1% HEK-a 6940 >7.0  91.9 ±8.6% HEK-a 6937 >7.0 59.8% ± 4.4% HEK-a 6539 >7.0 77.5% ± 3.1%

In summary, the above experiments demonstrated: clotting was stimulatedup to 4-fold by activating pairs of clotting factors, with no furtherstimulation using three activating pairs of clotting factor; PAMAMdendrimer-based, polyP-containing procoagulant nanoparticles weresynthesized and tested for stability and activity; polyP-containingpolystyrene procoagulant nanoparticles were synthesized and tested forstability and activity; polyP-containing gold procoagulant nanoparticleswere synthesized and tested for stability and activity; the synthesizednanoparticles had a 125+/−25 nm particle diameter and 18.2 nm pore size;porous silica was determined to be biocompatible with human cells;particle synthesis procedures for delivery of thrombin, which has ahydrodynamic radius of 8.4 nm, were developed; titania particles with225+/−50 nm average diameter were synthesized; polyP chains wereattached to silica and titania nanoparticles using Lewis acid-basechemistry and APTES-EDAC mechanism; and procoagulant activity of silicaand polyP-bound silica were quantified.

Example 3

Experiments were performed on solid silica nanoparticles ranging from10-150 nm in diameter. The silica acted as a scaffold upon which theprocoagulant agents attached. Particles of this size can flow throughsmall vessels in the blood stream.

Gold nanoparticles of 10 nm and 15 nm diameter were selected as baseparticles in addition to the 5 nm gold nanoparticles that were initiallyinvestigated. The maximum numbers of polyphosphate chains that can beadded to each particle based on theoretical analysis are: 64 and 144 forthe 10 nm and 15 nm gold particle, respectively. The different sizeparticles contained distinct, known numbers of polyphosphate chains. Incertain embodiments, nanoparticles bigger than a threshold size withconjugated polyphosphate more than the critical number triggered bloodclotting.

Experiments were performed on solid silica nanoparticles under 200 nm asthe delivery agent. Polyphosphate was attached to a silica scaffoldusing the Lewis acid-base properties of silica and polyphosphate. 70 merlength polyphosphate (P70) was used, as this length roughly correlatesto the size of polyphosphate secreted by human platelets duringclotting.

Additionally, thrombin was attached to solid silica using a proteincross-linker. The mechanism for attachment is shown in FIG. 44. Byfunctionalizing silica with 3-Aminopropyltriethoxysilane (APTES), thesilica acted as a protein for cross-linking purposes.

Experiments were performed to test solid silica nanoparticles withcovalent linkages to the coating. The first system was polyphosphateattached datively to bare oxide or covalently to aminopropyl terminatedsilica nanoparticles. The second was a linker system for protein and/orpeptide coupling. The coupling results used a protected thioacetylcoating on the particles and a thiol reactive ortho-pyridyl disulfide(OPSS) carried on lysines of the protein. Hydroxylamine deprotection ofthe particles was verified using the thiol sensing colorimetric assay(FIG. 45). OPSS-thrombin and dye-labeled albumin-OPSS serve as modelproteins (FIG. 44). Silica-thioacetyl was prepared in two steps fromsilica. Thiol deprotection was verified by 5,5′-Dithiobis(2-nitrobenzoicacid) (DTNB). Sample D had reagents but no silica, and in sample E,silica-SATP generated intense color indicating successful deprotection.

Polyphosphate polymers of a wide variety of polymer lengths wereprepared by large-scale preparative electrophoresis forsize-fractionating polyphosphate. These materials were used as one ofthe procoagulant payloads for the nanoparticles. In some instances, theprocoagulant activity may depend on the polyphosphate polymer lengths.Linking chemistries for covalently attaching polyphosphate to targetingmolecules and nanoparticles included indirect coupling by firstattaching polyamines to the terminal phosphates, and then usingamine-reactive probes to link to the terminal amino groups.

The same reaction scheme was used to conjugate polyphosphate onto goldnanoparticles. Ratios of the reactants (thiol-polyphosphate to goldnanoparticles) and gradients of solution ionic strength were varied toproduce maximum conjugation of polyP onto gold particles (5 nm, 10 nm,and 15 nm). Separation of the conjugates from free polyphosphate wasperformed by centrifugation. Centrifugation was tested at various polyPand gold nanoparticle concentrations to (1) remove free polyphosphateefficiently; (2) prevent particle aggregation; and (3) to minimize lossof gold nanoparticles. After the reaction between thio-boundpolyphosphate and gold nanoparticles, as well as after centrifuging, TEMimages were taken to determine whether smaller non-visible aggregateshad formed. The images indicated that aggregation pre-centrifugation wasminimal with a small percentage of 2 and 3 particle clusters.

Experiments showed that a roughly 250 nm solid silica nanoparticle boundto polyphosphate accelerated clotting compared to recalcified plasmausing thromboelastography (TEG). Experiments were performed to furtherquantify the procoagulant activities of silica, polyphosphate, andpolyphosphate bound to silica. Various sizes and concentrations ofsilica were tested. P70 was bound onto a smaller silica scaffold. Evenat a mg lower concentration, the silica-P70 TSP showed a decrease in Rtime by about 0.5 min.

Experiments were performed to test the procoagulant activity ofpolyphosphate in solid and solution phases without a scaffoldattachment. The tests showed increased clotting times and weakened clotstrength when compared to recalcified plasma, which indicated that thepolyphosphate of relatively short polymer sizes may be attached to ascaffold to function as a procoagulant. Attaching multiple copies ofthese shorter polymers to the same nanoparticle may allow a localizedassembly of multiple clotting proteins similar to what would be observedwith a single, long polyphosphate polymer.

Example 4

Experiments were performed on silica nanoparticles (SNPs). The silicaacted as a scaffold upon which the procoagulant agents attached.Particles of the studied size can flow through the smallest vessels inthe blood stream. Silica nanoparticles between 1-10 nm and 50-150 nmwere tested.

The effect of the silica particles' size and concentration oncoagulation was measured. Particles above 50 nm were synthesized in thelaboratory following a modified Stöber method (Stober W., et al., J.Colloid & Interface Sci., 26(1), 62-69) and recovered usingcentrifugation. The different nanoparticle sizes were obtained byvarying the amounts of tetraethoxysilane (TEOS) and ammonia. SigmaAldrich supplied Ludox silica nanoparticles below 10 nm. Silicananoparticles below 50 nm were isolated by ultrafiltration andultracentrifugation.

Size-dependent clotting experiments were performed to compare thevarious silica particles at a fixed concentration of 0.68 mg/mL, whichwas defined in other experiments to be in the range of high activity(FIG. 46). A minimum R value, the time to initial clot formation,occurred at a particle size of 55 nm. The 55-nm particles showed an Rvalue of 3 min (FIG. 47), which was suitable for testingsurface-attached polyphosphate.

Concentration experiments focused on 55-nm silica particles, tested atconcentrations of 0.14 mg/ml, 0.34 mg/ml, 0.68 mg/ml, 1.35 mg/ml, and2.70 mg/ml. The resulting data (FIG. 47) identified ˜0.6 mg/ml baresilica as the threshold for a minimization of R. At this concentration,the R value averaged 3 min. The R value remained near 3 min for doublethe silica (1.35 mg/ml) and then rose slightly to 3.5 min at 2.70 mg/ml.High concentration may result in aggregation or dilution of plasmafactors over the surface area. The particles were stable over a wideconcentration range (FIG. 48) and were testing in buffers and high-salt,serum conditions.

The R value was dependent on concentration until the threshold conditionwas met, over which R remains low and stable.

PolyP45-labeled gold nanoparticles (5 nm, 10 nm, 15 nm, and 50 nm) wereseparated from free polyP45 by centrifugation. More than 90% of thepolyP-labeled gold nanoparticles were recovered and 99% of the polyP45that was not covalently bound to the particles was removed.

As shown in FIG. 47, silica-based surfaces enhanced clotting above athreshold concentration. Different types of coatings were tested.APTES-functionalized silica was used to link with a variety ofcompounds. Amine functionalization of the surface was used and clottingeffects were compared provide a pro-coagulant surface while introducingconjugate handles for attachment of polymers, peptides, or proteins.

Silica Nanoparticles (SNP) (FIGS. 46-48)

-   -   1) -polyphosphate (FIG. 49)    -   2) -APTES; Low to high (FIGS. 50 and 51)        -   a. -APTES-polyphosphate        -   b. -APTES-PEG (FIG. 49)        -   c. -APTES-PEG-Peptide        -   d. -APTES-link-Peptide        -   e. -APTES-link-Peptide-PEG

The polyphosphate used in FIG. 49 was a ˜70-mer length (P70) that waschosen for its similarity to the size of polyphosphate secreted by humanplatelets during clotting. P70 directly adsorbed to silica was found toslightly increase the particle size (by several nm). Polyphosphate maybe attached to silica via an APTES bridge, based on the covalentderivatization technology for polyphosphate. Silica nanoparticles withAPTES are shown in FIGS. 50 and 51. APTES-specific anchoring may yieldhigher surface density or an improved conformation, e.g., brush anchoredby only terminal phosphates.

FIG. 50 shows the clotting factor R for a series of APTES-Silica(SNP-NH₂). The polyphosphate can be coupled using EDC, and pH-dependentzeta potential can be monitored relative to the SNP-NH₂ startingmaterial as in FIG. 50. The same APTES strategy can be used as a pointfor attaching PEG, peptides for targeting or enzyme activation, and/orproteins. Reactive linkers can be employed, for example amine reactiveNHS-linker-Maleimide or NHS-linker-OPSS for subsequent thiol attachment.Thiols can be carried on the dye-labeled peptides or introduced intoproteins using 2-iminothiolane or N-Succinimidyl S-Acetylthiopropionate(SATP).

In certain embodiments, a protease-sensitive coating can be removed onceabove-threshold conditions are met, e.g., a prothrombinase-sensitiveIEGR peptide linker sequence. The coating may includelarge-molecular-weight PEGs attached through peptide linkers to a sharedsilica core nanoparticle, whose surface activity is reduced by thepresence of the PEG. Fluorescein-labeled peptides can be used forquantification after coupling. PEG or other passivating polymers may beused to (i) increase the half-life of silica in the blood stream, (ii)reduce cellular uptake, and (iii) reduce protein adsorption to theactive, yet hidden surface.

Experiments were performed to test SNPs with and without adsorbed polyp.The SNPs with attached polyP had increased procoagulant activitycompared to SNPs without polyP.

Cystamine (a disulfide compound with two terminal primary amines) wasconjugated with polyP45 at reaction efficiencies of 90% by buffering thereaction at pH 9 with MES and allowing the reaction to proceed at roomtemperature for 24 hours. The binding of polyphosphate to cystamineoccurred via phosphoramidate bond formation between the terminalphosphate and the primary amine. Next, dialysis (MWCO 2000) was used toremove the unreacted cystamine. The conjugate was then added to the goldnanoparticles to replace the citrate. By controlling the reaction timeand ionic strength of the suspension, the number of polyP chainsconjugated to one nanoparticle can be varied. The following polyP45-Aunanoparticles were synthesized and tested on a coagulometer to measureFactor X-mediated clotting activities, as outlined in Table 4, below:

TABLE 4 polyP45-Au nanoparticles NP Vol- Sample Diameter Contains MonoPAu Agg. ume Name (nm) PEG (μM) (nM) # (uL) 56_10 10 No 19.48 15.5 28 70057_10 10 No 20.3 14.7 30.8 500 59_10 10 No 31.4 12.9 54.2 380 M9_10 10No 10.6 6.1 38.7 930 M9_15 15 No 12.6 4.95 56.6 700 10_A1D 10 No 10.911.3 21.6 210 10_A1D- 10 Yes 9.8 16.2 13.4 250 2:1peg 15_A1D 15 No 4.962.61 42.2 600 50_A1D 50 No 6.93 0.245 628 100 10_10 10 No 53.5 17.4 68500 16_10 10 No 9.8 14.7 14 700 9_5 5 No 56 56 22 640 14_5 5 No 4.59 781 940

Based on the tests of the above samples: (1) there was no correlationbetween clotting time and aggregation number for 10 nm particles atconstant phosphate concentration (9.8 μM) (FIG. 52); and (2) Clottingtime depended on phosphate concentration (FIG. 53).

Experiments were performed on mechanisms for attaching polyphosphate(P70) to the surface of solid silica nanoparticles. APTES was used toattach the P70. Conjugation of PEG to the amines modulated the R value.In certain embodiments, proteolytic cleavage could unmask and expose thepro-coagulant surface. For example, enzyme-recognition peptides may beused to hold the PEG to a low-APTES silica. In a reverse orientation,where peptide is on the outer tip of the PEG, the damaged vascularsurface, activated cell surfaces, or fibrin may be targeted. Proteinssuch as thrombin and tissue factor similarly masked by PEG may becarried in a protected form by nanoparticles to the site of interest.

Bare silica was tested to determine clotting values based on size andconcentration (FIGS. 46-48). The same were used on P70-bound silicananoparticles to identify thresholds that induced coagulation (FIG. 49).In certain embodiments, the short clotting times of P70-bound silica mayfacilitate treatments that target an internal wound. For example,particles whose concentrations are below the threshold level may be usedto prevent undesired general clotting when in the general circulation.Materials may be spatially targeted to specific surfaces (e.g., woundedendothelial) to concentrate the material to above-threshold clottingbehavior. Protecting the particles with PEG, which is cleaved off byfactors present at the target site, may facilitate control over thelocation where coagulation is initiated.

Example 5

Experiments were performed on the conjugation reaction to attachpolyphosphate on gold nanoparticles and the purification procedure. Thepurification process of gold nanoparticles involved the removal ofexcess, free floating polyphosphate left in the solution. A microcentrifuge (Labnet Spectrafuge 16M Microcentrifuge, LabnetInternational, NJ) was used to purify the samples. The centrifugingstudies were done first to obtain the conditions for the removal of ˜99%free floating polyP and recovering most of the gold particles (˜90%)without causing aggregation. Depending on the size of the goldnanoparticles, the following conditions were used (Table 5):

TABLE 5 Size-dependent centrifugation conditions. Au NPs size Rpm Gforce Time to pellet Centrifuge 10 nm 8600 6000 100 min  3x 15 nm 100008176 30 min 2x 50 nm 8000 5223 10 min 3x

The pelleting time, t, was calculated using the flowing equation, (1)

$\begin{matrix}{t = \frac{k}{s}} & (1)\end{matrix}$

where k is the pelleting efficiency of the rotor and S is thesedimentation coefficient. The pelleting efficiency (k) was calculatedby using the equation 2 below,

$\begin{matrix}{k = \frac{2.53 \times 10^{11}\left( {\ln\left( \frac{r_{\max}}{r_{\min}} \right)} \right)}{({RPM})^{2}}} & (2)\end{matrix}$where rmax and rmin are the maximum and minimum radii of the centrifugerespectively, and RPM is the speed in revolutions per minute. Ther_(max) and r_(min) values were measured based on the type of thecentrifuge used.

The sedimentation coefficient, S, can be calculated by using equation,

$\begin{matrix}{S = {\frac{2\left( {\rho_{s} - \rho_{l}} \right)}{9\eta}\left( \frac{d}{2} \right)^{2}}} & (3)\end{matrix}$where ρs and μl are the densities of gold nanoparticles and water,respectively, η is the viscosity of water, and d is the diameter of goldnanoparticles.

After each centrifugation, the supernatant containing free-floatingpolyP was removed and the pellets were re-suspended with 2 mM MES at pH9 to ensure the stability of the polyP-cystamine ligand. The pH of thesamples affected the P-N bond hydrolysis. As such, the particles wereresuspended with the buffer at the pH higher than 7. The resuspendedsamples were vortexed for 30 seconds and the centrifugation was repeatedas specified in Table 6.

TABLE 6 Size-dependent centrifugation conditions. Centrifuge Au NPs sizeRpm G force Time to pellet repeat 10 nm 8600 6000 100 min  3x 15 nm10000 8176 30 min 2x 50 nm 8000 5223 10 min 3x

Experiments were performed on multifunctionalized silica nanoparticles(SNPs) as well as titania (TNP) and silica coated silver nanoparticles(Ag@SNP). The inorganic materials acted as the scaffold upon which theprocoagulant agents attached. Nanometer-scale particles can flow throughsmall vessels in the blood stream. Selective covalent PEGylation may beused to minimize adverse effects. FIG. 54 shows representative TEMimages of the SNP synthesized with mean diameter dimensions in the rangeof sub-100 nm.

The effect of the silica particles' size and concentration oncoagulation were measured. Particles above 10 nm in mean diameter wereselective-size synthesized following a modified Stöber method andrecovered using centrifugation. The different nanoparticle sizes wereselectively obtained by varying the amounts of tetraethoxysilane (TEOS)and ammonia (NH₄OH). FIG. 55 shows the particle size as a function ofthe NH₄OH percentage at fixed TEOS and ethanol concentrations. Ludoxsilica nanoparticles below 10 nm (Sigma-Aldrich) were also examined.Silica nanoparticles below 50 nm were isolated by ultrafiltration andultracentrifugation. Yields were over 50% for syntheses using more than4% NH₄OH (FIG. 56). The smaller amount of ammonia used to make thesmallest particles may inhibit catalysis of the TEOS in the hydrolysisreaction. Experiments synthesizing particles below 20 nm also exhibiteda bimodal size distribution when measured using DLS. The bimodal sizesdistribution may be due to the low concentration of ammonia.

Tracking the delivery of nanoparticles to the wound using imaging may befacilitated by using silver nanoparticles coated with silica of about 10nm thickness (Ag@SNP, FIG. 57). Initial experiments using Ag@SNP showeda delayed average R value of 13.8±1.3 min. In some instances, a thickersilica shell may be used to increase the concentration in the clottingessays. In addition to silver, magnetic nanoparticles may also be usedfor imaging as well as cluster control.

In addition to solid non-porous nanoparticles, high surface area(500-1000 m²/g), large-pore mesoporous nanospheres (MSN) may be used todeliver procoagulant proteins such as thrombin or tissue factor, orprothrombin to wounds.

Anatase titania particles were synthesized by the sol-gel method and byvarying the amount of acid catalyst added to each synthesis. Theresulting titania nanoparticles were tested using X-ray diffraction andDLS to determine the form (amorphous, anatase or rutile) and size of thetitania.

PolyP45-labeled gold nanoparticles (5 nm, 10 nm, 15 nm, and 50 nm) wereseparated from free polyP45 by centrifugation. More than 90% of thepolyP-labeled gold nanoparticles were recovered and 99% of the polyP45that was not covalently bound to the particles were removed.

High MW polyphosphate (also known as “insoluble phosphate glass”) wasused as the starting material for preparing polyphosphate fractions ofthe desired polymer lengths. The high MW polyphosphate was largelyinsoluble in water, as it consisted mostly of polymers that werethousands of phosphate units long. Suspending the material in anunbuffered LiCl solution and heating to 100° C. for several hours withconstant stirring resulted in the majority of the polyphosphate goinginto solution. A time-dependent shortening of the average polymer lengthof the polyphosphates during heating was observed. The slightly acidicpH of the polyphosphate solutions resulted in a mild acid hydrolysis ofthe polymers. The speed of hydrolysis appeared to increase with time,which was the result of the gradual acidification of the solution as thepolyphosphate polymers were being hydrolyzed. The gradual acidificationof the polyphosphate solution therefore gradually accelerated the rateof polyphosphate hydrolysis.

Hydrolysis of the phosphoanhydride bonds in polyphosphate can also behydrolyzed by base, and as such the gradual acidification of thesolution may gradually slow the rate of hydrolysis, in contrast to acidhydrolysis whose rate increased with time. Experiments were performed byadding varying amounts of LiOH to the LiCl solutions in whichpolyphosphate was stirred at 100° C. A gradual, time-dependentshortening of polyphosphate chains as a function of the starting LiOHconcentration was observed. As such, MW polyphosphate was suspended,with stirring, in a combination of LiCl and LiOH at 100° C. until thedesired mean polymer lengths were obtained. This method was robust andreproducible, and was scalable to gram quantities of polyphosphate andhigher.

The conditions for solubilizing and partially hydrolyzing polyphosphatewith LiOH/LiCl were adjusted to yield the desired mean polymer lengths.In some instances, the method resulted in polyphosphate preparationswith heterogeneous sizes. Differential precipitation of thepolyphosphates using varying combinations of acetone and salt (e.g.,NaCl, KCl and LiCl) concentrations may be used. In addition,combinations of varying concentrations of isopropanol and NaCl producedrelatively narrow size fractions of polyphosphate, starting with high MWpolyphosphate that had previously been solubilized and partiallyhydrolyzed using the LiOH/LiCl procedure outlined above. Using theseconditions polyphosphate, from ˜40 to ˜1500 phosphate units long, ingram quantities and above was obtained.

Functionalizing the silica and anatase titania nanoparticles withpolyphosphate or thrombin may enhance the procoagulant nature of theparticles. Polyphosphate readily attached to the surface of inorganicnanoparticles to create a more potent agent. In addition topolyphosphate, thrombin may be attached to silica nanoparticles throughthe use of 3-aminopropyl triethoxysilane (APTES) and proteincross-linkers. Types of coatings that may be used include:

SNP (FIGS. 54-56 and 58)

-   -   3) -polyphosphate; different size (FIGS. 59-61)    -   4) -APTES; low to high (FIG. 62)        -   a. -APTES-polyphosphate        -   b. -APTES-link-PEG (FIG. 62)        -   c. -APTES-PEG-Peptide        -   d. -APTES-link-Peptide        -   e. -APTES-link-Peptide-PEG (FIGS. 63-64)

TNP (FIG. 65)

-   -   1) -polyphosphate; different size (FIG. 66)    -   2) -APTES; low to high (same a to e) (FIG. 67)    -   Ag@SNP (FIG. 57)    -   MSN

In comparison to external hemorrhage, internal hemorrhages are notdirectly accessible and should be accurately targeted. The particles aredesigned to be injected into the bloodstream and to only target anddeliver at the bleeding sites. A second functionalization may be used toprotect the nanoparticles from initiating clotting in healthy vessels.Nanoparticles designed for drug delivery may be coated with polyethyleneglycol (PEG) to prevent unwanted activation. PEGylated nanoparticlesincreased the half-life of silica in the blood stream, limited cellularuptake, and limited protein adsorption to the active, yet hiddensurface. At the wound, the particle may release the PEG and initiateclotting. A peptide with an IEGR sequence that connects the particle tothe PEG (FIG. 63) may be used. Activated Factor X (FXa) cleaves thepeptide at the IEGR sequence, removing the PEG and leaving the activatedTSP. As FXa only exists above threshold at bleeding sites, the targetingmechanism ensures that the TSP activates only where necessary.

A reverse orientation where the peptide is on the outer tip of the PEGmay be used to target a damaged vascular surface, activated cellsurfaces, or fibrin, for example. Thrombin and tissue factor similarlymasked by PEG may be used if they can be carried in a protected form bynanoparticles to the site of interest.

Polyphosphate was attached to its nanoparticle scaffold via an APTESbridge, based on the covalent derivatization technology forpolyphosphate. APTES-specific anchoring of polyphosphate may yield ahigher surface density and an improved conformation. The polyphosphatecoating may increase biocompatibility and specificity, conjugationversatility, and overall targetability relative to bare silica.

Experiments were performed on nanoparticles where a polyphosphate with a˜70-mer length (P70) was bound to silica in order to identify thresholdsto induce coagulation. Short clotting times of P70-bound silica mayfacilitate targeting an internal wound. Particles whose concentrationsare below the threshold level may be used in order to prevent undesiredgeneral clotting when in the general circulation. Spatially targetingthe materials to the specific surfaces (e.g., wounded endothelial) maybe used to concentrate the material to above-threshold clottingbehavior. Protecting the particles with PEG, which is cleaved off byfactors present at the target site, would add an additional level ofcontrol.

Experiments were performed to test procoagulant nanoparticles with andwithout adsorbed polyP, and to quantify the procoagulant activity of thenanoparticles with regard to their ability to trigger the contactpathway of blood clotting (clot initiation) as well as their activitytoward accelerating the ability of FXa to clot plasma (clotpropagation).

PolyP70 was used to synthesize a polyP-disulfide conjugate to covalentlyattach to gold nanoparticles. The binding of polyphosphate to cystamineoccurred via phosphoramidite (P—N) bond formation between the terminalphosphate and the primary amine. The hydrolysis study of the P—N bondwas performed to test for the stability of the polyP-cystamine ligand.The pH of the reaction was adjusted to look at the pH effect on thehydrolysis. The stability was quantified by the fluorescamine assaywhich detected the amount of unreacted cystamine. The increase in theamount of unreacted cystamine indicated that hydrolysis had occurred,indicating that the polyphosphate moiety was cleaved from cystamine.Based on the results as shown in FIG. 68, the P—N bond hydrolyzed inacidic conditions at pH 6.02. It was stable above pH 7.

This hydrolysis study of the polyP-cystamine ligand was used to optimizethe conditions for the gold-polyP reactions. The pH of these reactionswas adjusted to be higher than 7 by adjusting them with 500 mM MESbuffer at pH 9. In addition, the purification process was alsooptimized. The nanoparticles were resuspended with 2 mM MES buffer at pH9 to ensure that the polyP was still attached to gold nanoparticles viathe cystamine linker. The above conditions were used to synthesize bothpolyP45- and polyP70-gold nanoparticles with various aggregationnumbers. The volumes of the gold-polyP reactions were also increased toobtain higher monophosphate concentration in order to increase thesensitivity of the blood clotting measurements.

The following polyP45-Au (10 nm, 15 nm, 50 nm) nanoparticles weresynthesized and tested on a coagulometer to measure clotting time usinghuman plasma.

TABLE 7 The sample conditions for polyP45 conjugated to goldnanoparticles (10 nm, 15 nm, and 50 nm). Au UV-vis MonP particle Aggre-UV-vis Peak after Vol- PolyP conc. conc. gation Peak for centri- umeSample Type (uM) (nM) # bulk Au fuging (uL) 10_1 45 80.00 104.7 16.98519 523 240 10_2 45 80.00 90.34 19.68 519 524 320 15_1 45 80.00 29.2960.70 521 523 290 15_2 45 80.00 37.33 47.62 521 523 340 50_1 45 80.003.74 475.34 533 533 390 50_2 45 80.00 2.03 875.75 533 533 390

The following polyP70-Au nanoparticles were synthesized (Table 8; seeFIG. 102) and were tested for procoagulant activities.

Results (FIG. 69) using the particles in Table 8 showed that 50 nm goldparticles with the highest aggregation number had the highestprocoagulant activities (i.e., shortest clot times when tested at ˜6.5uM phosphate). These results demonstrated that the procoagulant activityof the gold particles was modulated by the number of polyphosphatemolecules/particle.

Attaching polyphosphate P70 to the surface of solid silica nanoparticlesthrough APTES may facilitate specific functionalization ofthreshold-switchable particles, TSP, which induce clotting solely at thedesired wound site.

In addition to P70, linger chain polyphosphates (˜0.700-mer, P700) maybe used. Polyphosphate with a size range above 500-mers initiated thecontact or intrinsic pathway of blood clotting. The P700 can be attachedto the scaffolds using the same methods described above.

Clotting experiments described above compared the silica particles ateither a fixed concentration of 0.68 mg/mL (25 mg/mL stock solution) orat a fixed size of 55 nm to determine high activity range boundaries.Each particle formed an initial clot (R) between 3 and 5 min. Thethreshold for minimum R value occurred at a particle size of ˜30 nm.

Using 55-nm silica particles, ˜0.6 mg/ml (30 mg/mL stock) bare silicawas identified as the threshold required to minimize R. At thisconcentration, the R value averaged 3 min (compared to 12-16 minuteswithout silica). The R value remained near 3 min for double the silica(1.35 mg/ml) and then rose slightly to 3.5 min at 2.70 mg/ml. Theincrease in R at high concentrations may have occurred as a result ofparticle aggregation or dilution of plasma factors over the particle'ssurface area. Regardless of concentration, DLS tests confirmed that theparticles maintain stability and size. At low particle concentrations,the R value was high. As the particle concentration increased, Rdecreased until the threshold condition was met. At this point, Rremained low and stable until the particle concentration became highenough to inhibit clotting. FIG. 58 shows a narrow range ofconcentrations near the optimum value for different particle size SNP.In addition to the clotting time (R) other parameters were alsoevaluated, such as rate of clot formation, and clot size, since theagents attached on the particle might not affect the initial clotformation time, but could accelerate the clotting when initiated orcould result in the formation of a bigger clot.

The polyphosphate used in the assays was a ˜70-mer length (P70) chosenfor its similarity to the size of polyphosphate secreted by humanplatelets during clotting, and which activate FV. P70 directly adsorbedto silica was found to slightly increase the particle size (by severalnm). Samples of bare and P70-bound 55-nm silica nanoparticles weretested for polyphosphate quantification and coagulation. The results areshown in FIGS. 59A and 59B, which show that P70-bound SNPs significantlydecreased clotting time when compared to bare SNP.

The clotting properties of the anatase titania were also tested. Theclotting times of the four acid-catalyzed syntheses shared similarclotting times. The titania formed at neutral pH exhibited a lowerclotting time (T4 in FIG. 65). Concentration-dependent experiments alsoconfirmed that when diluted, the clotting activity diminished. Whenfunctionalized with P70, the T4 samples further reduced clotting time(FIG. 66).

Clotting tests were performed using FXII deficient plasma (FIG. 60) tostudy the mechanism by which P70-bound nanoparticles induce clotting. Asthey activate clotting through FXII activation and the intrinsicpathway, the bare nanoparticles do not induce clotting in the FXIIdeficient plasma. With the intrinsic pathway blocked, coagulation onlyoccurred through the addition of tissue factor (TF) and the extrinsicpathway. Since P70 accelerated coagulation through FVa, a combination ofTF and P70-bound silica improved clotting via the ability ofpolyphosphate to accelerate the propagation phase of blood clotting.Various mixtures of TF and nanoparticles were compared. The two lowestclotting times occurred as a result of either 1 ng/mL TF or 0.5 ng/mL TFmixed with 0.676 mg/mL P70-bound silica. Though the two conditionsshared a similar clotting time, the P70-bound silica rapidly acceleratedclot growth as illustrated by the larger coagulation index score (FIG.61). The P70-bound silica also gave reproducible conditions, which mayfacilitate a reduction in adverse side-effects. The tissue factor formeda small clot rapidly upon addition to plasma, but the clot grew at aslow pace. These tests showed that even under adverse conditions the P70bound particles quickly increased clotting through mediating FXa andthrombin. As such, polyphosphate can accelerate thrombin production atan in progress bleed and thus limit blood loss.

When bound to the nanoparticle surface, APTES and other cross-linkersreduced the active surface for coagulation (FIGS. 62 and 64).Experiments were performed to vary the ratio of APTES to silica in orderto optimize a TSP that would retain a dual nature—inert in healthy bloodvessels and procoagulant when activated. When functionalized solely withAPTES, the TSP retained its procoagulant nature. When PEG attached tothe TSP via the APTES bridge, the TSP was protected. Using 5 k or 20 ksized PEG decreased clotting times so that they were comparable to thatobtained using recalcified plasma. Replacing silica with titania as thescaffold resulted in similar clotting times (FIG. 67).

A TSP was prepared that remained unactivated in healthy blood vessels,while being activated at a wound site in order to obtain an effectiveinternal bleeding therapeutic agent that is only active at the bleedingsite while remaining unactivated in healthy blood vessels. FIG. 64 showsthat, apart from the APTES, the nanoparticles remained active even whenthe SPDP linker and the peptide were attached, since the clotting timeremained low. When the PEG was attached the clotting time was comparableto that of recalcified plasma without the particles, thus establishingthat the PEGylated nanoparticles with PEG molecular weight greater than5 k were non-coagulant. Enzymes may be used to cleave the peptide andrelease the PEG. For example, an IEGR sequence in the peptide and FXa asthe enzyme may be used. The proteolytic activity of the enzyme can bequantified by fluorescence and its reaction rate (enzyme kinetics)compared with TCEP, a potent versatile reducing agent.

In addition to TEG, the coagulation threshold response was tested usinga thrombin-specific blue coumarin dye. A small concentration of dye wasadded to the recalcified plasma. As clotting progressed and thrombinactivated, the thrombin cleaved the coumarin dye causing the solution tofluoresce. For instance, the thrombin burst signified by thefluorescence may indicate clot formation. A fluorescence microscopecaptured the qualitative change as shown in FIG. 70. A microscope and/ora plate reader was used to monitor clotting through the dye'sfluorescence. The plate reader can measure up to 96 samples at the sametime. This allowed the study of several TSPs along with a standardthrombin concentration concurrently to determine the most active TSP.Particles clustered together as well as those that are finely dispersedin plasma can be studied.

Example 6

Threshold-Switchable Particles (TSP)

Experiments were performed to develop targeted delivery of nanoparticlesfunctionalized with controlled amounts of polyP. These tunable particlesare able to selectively target sites of injury in response toappropriate stimuli such as a drop in temperature without the inductionof clotting at other locations in the body.

High MW polyP preparation (also known as “insoluble sodium phosphateglass”) was used as the starting material for preparing polyP fractionsof the desired polymer lengths. High MW polyP was largely insoluble inwater, as it consisted mostly of polymers that were thousands ofphosphate units long. High MW polyP was suspended in nonbuffered 100° C.0.25 M LiCl solution with constant stirring, and resulted in themajority of the polyP solubilizing and going into solution. Atime-dependent shortening of the average polymer length of the polyPsduring heating was observed (FIG. 71). The slightly acidic pH of thepolyP solutions resulted in a mild acid hydrolysis of the polymers. Thespeed of hydrolysis appeared to increase with time, which was the resultof the gradual acidification of the solution as the polyP polymers werebeing hydrolyzed. The gradual acidification of the polyP solutiongradually accelerated the rate of polyP hydrolysis.

Hydrolysis of the phosphoanhydride bonds in polyP was also catalyzedunder basic conditions, and the gradual acidification of the solutionduring polyP hydrolysis gradually slowed the rate of hydrolysis, incontrast to acid hydrolysis whose rate increased with time. Varyingamounts of LiOH were added to the LiCl solutions in which polyP wasstirred at 100° C. A gradual, time-dependent shortening of polyP chainsas a function of the starting LiOH concentration was observed, which wasaccompanied by the “insoluble” polyP polymers becoming water-soluble(FIG. 72). High MW polyP was suspended, with stirring, in a combinationof LiCl and LiOH at 100° C. until the desired mean polymer lengths wereobtained and essentially 100% of the material was solubilized. Thismethod was robust and reproducible, and scalable to gram quantities ofpolyP and higher.

The conditions for solubilizing and partially hydrolyzing polyP withLiOH/LiCl were adjusted to yield the desired mean polymer lengths. Insome instances, the method resulted in polyP preparations ofheterogeneous sizes. Experiments were performed to furthersize-fractionate polyP after base hydrolysis. Differential precipitationof polyP using varying combinations of acetone and salt concentrations(e.g., NaCl, KCl and LiCl) were tested. In addition, varyingconcentrations of isopropanol and NaCl allowed the production ofrelatively narrow size fractions of polyP, starting with high MW polyPthat had previously been solubilized and partially hydrolyzed using theLiOH/LiCl procedure outlined above (see FIG. 73 for an example). Theabove conditions were used to obtain size ranges of polyP from ˜40 to˜1500 phosphate units long, in gram quantities and above.

Citrate Gold Nanoparticle Synthesis

Gold nanoparticles with an average diameter of 10 nm, 15 nm, and 50 nmwere synthesized by using the Turkevich Method. The average size andsize distribution of the gold nanoparticles were confirmed by dynamiclight scattering (DLS) and UV-vis absorbance (Table 9 and FIGS. 74A-C).

TABLE 9 Comparison of 10 nm, 15 nm, 50 nm gold nanoparticles andcommercial samples with their UV-vis peak, DLS- measured particles sizeand polydispersity Mole Gold Reaction Poly- ratio Concen- Temper- UVdisper- (Cg:Cc) tration ature Peak Size sity Reaction 1:4  0.4 mM 95° C.520 nm 13.6 nm 0.175 A 60° C. 522 nm 14.7 nm 0.25 Reaction 1:3  0.4 mM95° C. 522 nm 17.2 nm 0.178 B 60° C. 522 nm 18.3 nm 0.227 Reaction 1:1 0.4 mM 95° C. 533 nm 35.7 nm 0.196 C 60° C. 534 nm 37.9 nm 0.256Commer- 0.29 mM 519 nm 11.3 nm 0.24 cial_10 Commer- 0.24 mM 521 nm 15.6nm 0.19 cial_15 Commer- 2.89 mM 532 nm 42.1 nm 0.11 cial_50PolyP-Gold Nanoparticle Conjugates

Attachment of polyP to gold nanoparticles was achieved by two-stagereactions. (1) PolyP was allowed to react with cystamine; (2)PolyP-cystamine conjugates were then reacted with gold particles viadisplacement of the citrate groups (FIG. 75, panel A, and FIG. 75, panelB). The primary amine-containing compounds like polyethylenimine,amine-PEG₂-biotyn, and spermidine were used to covalently attach primaryamine groups with the terminal phosphates of polyP via EDAC-meditatedreaction. This method was used for the coupling of polyP withcystamine—a disulfide molecule containing two primary amine groups. Thedisulfide moiety in cystamine then allowed for the attachment to gold.Various conditions (including temperature, reaction time, pH, and buffersolutions) were tested in order to optimize the reaction efficiency andyield.

The effects of polyP-gold nanoparticles (with different sizes and polyPaggregation numbers) on blood clotting kinetics were tested. Thefollowing control groups were selected to compare with polyP-goldnanoparticle conjugates: (1) free polyP with the same molecular weightat the same concentrations; (2) citrate gold nanoparticles withoutpolyP; and (3) PEGylated gold nanoparticles. Various aggregation numbersof polyP on gold nanoparticles were achieved by adding PEG thiol tocompete with polyP-cystamine for ligand replacement.

PolyP-Cystamine Conjugation Reaction

Various conditions (including temperature, reaction time, pH, and buffersolutions) were tested for the coupling reaction of polyP withcystamine. Polyp was allowed to react with cystamine at room temperaturefor 48 to 72 hrs. The pH for the reaction was about 8. A fluorescamineassay was used to test the amount of the unreacted primary amines oncystamine, which indicated the conjugation efficiency. The yield of thereaction was approximately 90% as seen in (Table 10).

TABLE 10 Conjugation efficiency of polyP and cystamine at various pHconditions. pH of Efficiency Efficiency Efficiency Buffer reaction (24h) (48 h) (72 h) MOPS (100 mM) 7.1 61.5% 65.0% 71.1% MOPS(100 mM) 7.672.7% 74.3% 76.7% MOPS(100 mM) 8.1 79.8% 87.3% 88.1% MOPS(100 mM) 8.583.5% 87.3% 88.6% MES(100 mM) 7.8 81.4% 89.5% —

The hydrolysis study of the P-N bond was carried out to test thestability of the polyPcystamine ligand. After 72 hours of reaction, thefluorescamine assay was performed to detect the concentration of theunreacted cystamine. An increase of free cystamine concentration afterthe pH adjustment of reactions indicated the hydrolysis of the P-N bond.The samples were tested for two weeks and quantified by thefluorescamine assay. The P-N bond hydrolyzed in acidic conditions at pH6.02. It was stable above pH 7 as seen in Table 11 below.

TABLE 11 Free cystamine concentration (μM) before and after pHadjustment Primary amine concentration (μm) Before pH After After AfterAfter pH adjustment 1 day 5 days 8 days 13 days 6.02 16.4 30.0 26.4 27.637.18 7.07 16.4 18.6 14.5 12.9 13.72 9.05 16.4 17.1 14.8 14.2 15.3110.01 16.4 17.2 14.8 12.7 14.73Reaction of polyP-Cystamine with Gold Nanoparticles

The polyP-cystamine conjugate was allowed to react with goldnanoparticles of various sizes (10 nm, 15 nm, 50 nm) by displacing thecitrate group. After 24 hrs of reaction the salt addition was initiatedto increase the coverage of the surface of the gold nanoparticle withpolyP. The slow increase in the salt concentration in the reaction overa period of four days (0.1M NaCl final concentration) allowed for thealready attached polyP to extend, creating more space for the unreactedligands to access the gold surface and thus resulting in an increase inthe aggregation number.

The purification process of gold nanoparticles involved the removal ofexcess, free floating polyP left in the solution. Centrifugation wasused to remove ˜99% free floating polyP and recover most of the goldparticles (˜90%) without causing aggregation. Depending on the size ofthe gold nanoparticles, the following conditions were found (Table 12).

TABLE 12 Size-dependent centrifugation conditions Centrifuge Au NPs sizeRPM G force Time to pellet repeat 10 nm 10000 8176 60 min 3x 15 nm 100008176 30 min 2x 50 nm 8000 5223 10 min 3x

The pelleting time, t, was calculated using the flowing Equation 1:

$\begin{matrix}{t = \frac{k}{s}} & (1)\end{matrix}$

where k is the pelleting efficiency of the rotor and S is thesedimentation coefficient. The pelleting efficiency (k) was calculatedby using Equation 2 below:

$\begin{matrix}{k = \frac{2.53 \times 10^{11}\left( {\ln\left( \frac{r_{\max}}{r_{\min}} \right)} \right)}{({RPM})^{2}}} & (2)\end{matrix}$

r_(max) and r_(min) are the maximum and minimum radii of the centrifugerespectively, and RPM is the speed in revolutions per minute. Ther_(max) and r_(min) values can be measured as shown in FIG. 76 based onthe type of centrifuge used.

The sedimentation coefficient, S, can be calculated by using Equation 3:

$\begin{matrix}{S = {\frac{2\left( {\rho_{s} - \rho_{l}} \right)}{9\eta}\left( \frac{d}{2} \right)^{2}}} & (3)\end{matrix}$

where ρ_(s) and ρ_(i) are the densities of gold nanoparticles and water,respectively, η is the viscosity of water, and d is the diameter of goldnanoparticles.

After each centrifugation, the supernatant was removed and the pelletswere re-suspended in a buffer of pH 7.4 to ensure the stability of thepolyP-cystamine ligand. As the hydrolysis study showed, the pH of thesamples affected P-N bond hydrolysis. Therefore, the particles wereresuspended with a buffer at a pH higher than 7.

Dynamic light scattering (DLS) and UV-vis spectroscopy were used tocharacterize the size and size distribution of the particles. Afterpurification/separation using centrifugation, concentrations of polyPwere measured using malachite green assay and concentrations of goldnanoparticles were obtained by UV-vis. Then aggregation numbers of polyPon the surface of gold nanoparticles were calculated based on the abovemeasurements. The following polyP-gold nanoparticles (Tables 13-15) weresynthesized and characterized.

TABLE 13 Synthesized polyP45-gold nanoparticles PolyP Gold size (# ofMonoP Particle Aggre- UV-vis Peak after repeating Conc. Conc. gationpeak for centri- Sample units) (μM) (nM) # bulk gold fuging P45_10nm_145 80.00 104.7 16.98 519 523 P45_10nm_2 45 80.00 90.34 19.68 519 524P45_15nm_1 45 80.00 29.29 60.70 521 523 P45_15nm_2 45 80.00 37.33 47.62521 523 P45_50nm_1 45 80.00 3.74 475.34 533 533 P45_50nm_2 45 80.00 2.03875.75 533 533

TABLE 14 Synthesized polyP70-gold nanoparticles Gold MonoP ParticleAggre- UV-vis Peak after PolyP Conc. Conc. gation peak for centri-Sample size (μM) (nM) # bulk gold fuging P70_10nm_1 70 75.00 31.98 33.50519 524 P70_10nm_2 70 75.00 153.50 6.98 519 528 P70_15nm_1 70 75.0016.14 66.38 521 522 P70_15nm_2 70 75.00 32.05 33.43 521 522 P70_50nm_170 75.00 2.068 518.09 532 533 P70_50nm_2 70 75.00 2.010 533.05 532 533

TABLE 15 Synthesized polyP-PEG (3:1)-gold nanoparticles Gold MonoPParticle Aggre- UV-vis Peak after Conc. Conc. gation peak for centri-Sample PolyP (μM) (nM) # bulk gold fuging P70_Peg_10nm_1 70 75.00 76.0014.1 519 525 P70_Peg_15nm_1 70 75.00 34.69 30.88 521 521 P70_Peg_50nm_170 75.00 3.83 279.7 532 533 P45_Peg_10nm_2 45 75.00 73.14 22.79 519 523P45_Peg_15nm_2 45 75.0 35.50 46.95 521 526Effects of polyP-Gold Nanoparticle on Blood CoagulationKinetics—Measured by Coagulometry.

The samples presented in the section above were tested for clottingusing coagulometry. The experiments performed focused on contact pathwayactivation. The activation of the contact pathway by polyP-goldnanoparticles was expressed in terms of equivalent long-chain polyPconcentrations (FIGS. 77 and 78). Long-chain polyP, which was aheterogeneous mixture of polymers greater than 500 repeating units,induced the intrinsic contact pathway of blood coagulation. The resultsindicated that the polyP45-gold nanoparticle samples had increasedprocoagulant activity compared to free-floating polyP45 of the sameconcentration in solution (FIG. 77). For each particle diameter of thepolyP45-gold nanoparticle samples that were synthesized, there was adirect correlation between aggregation number and increased procoagulantactivity. An increased activity of some 10 nm and 15 nm samples whencompared to 50 nm may be due to agglomeration of smaller size goldnanoparticles as indicated by the UV-vis peak shift after purification.In some instances, coagulation may depend on the surface density of theprocoagulant ligand polyP and the total surface area of the gold. Thecitrate gold nanoparticles also acted as contact pathway initiators dueto their negative surface charges, but to a lesser extent than thepolyP-gold nanoparticle conjugates.

The initial contact pathway activation coagulometry experiments forpolyP70-gold nanoparticles showed an increased activity of 50 nmpolyP70-gold samples when compared to free floating polyP70 in solution.There was no significant difference between the 10 nm and 15 nmpolyP70-gold nanoparticles and corresponding aqueous polyP70 (FIG. 78).The increased activity of the 50 nm polyP70-gold nanoparticle is shownin FIGS. 79-81. The fully PEGylated 50 nm gold nanoparticle as anegative control did not show procoagulant activity (FIG. 81). Thepartially PEGylated 50 nm polyP70-gold nanoparticle (with less polyPconjugated to gold nanoparticles) showed reduced procoagulant activityas expected, which was still more active than free-floating polyP70 atthe same concentration.

The results indicate that the polyP-functionalized gold particles aremore procoagulant than aqueous polyP of the same polymer length. 50 nmparticles induced blood coagulation.

Blood Coagulation Kinetics—Measured by Microplate-Based FlorescentAssays

Activation of the intrinsic pathway of blood coagulation was assessed byusing a fluorogenic thrombin substrate. A negative control containing noCa²⁺, and a positive control containing no polyP were also run tovalidate the experiment. To find the clotting time, the data were fittedto a sigmoidal function. The rate of thrombin substrate cleavage wasfound by taking the time derivative of the fluorescence intensity of thefitted curve, and the clotting time was defined in the relevant samplesto be one-half the maximum rate of substrate cleavage. Clotting kineticswas first measured using free polyP45. Clotting induction occurred onlyin the presence of calcium cations (FIG. 82).

Controlled Particle Aggregation by Using Thermosensitive Polymers

Controlled aggregation of smaller nanoparticles (˜15 nm) into biggerones (>50 nm) may trigger blood coagulation rapidly via contact pathwayinitiation as well as FV at the site of vessel or organ damage, whilenot significantly activating coagulation at other locations. Bodytemperature drop at the local trauma site due to the lack of blood andoxygen may be used to initiate controlled coagulation at the localtrauma site. Poly(acrylic acid) (PAAc) and polyacrylamide (PAAm) wereconjugated to gold nanoparticles through disulfide bonds. PAAc and PAAmare thermosensitive polymers with an upper critical solution temperature(UCST) around 33-35° C. When the temperature was below the UCST, PAAcand PAAm formed inter-molecular hydrogen bonding, which increased thehydrophobicity of the polymers and resulted in aggregation of theparticles and phase separation (FIG. 83, panel A). The process wasreversible. When the temperature was above the UCST, the hydrogenbonding disassembled and the phase separation disappeared.

Reversible Hydrogen Bonding

The assembly and disassembly of inter-molecular hydrogen bonding betweenPAAc and PAAm were observed (FIG. 83, panel B, to FIG. 83, panel D). Amixture of 10 wt % PAAc and 10 wt % PAAm was prepared at roomtemperature (˜20° C.), which was below the UCST. Hydrogen bonding formedimmediately and resulted in turbidity of the solution, which indicatedphase separation between the polymers and water (FIG. 83, panel B). Thesample was then heated up to 40° C. in a water bath. The solution turnedclear, which indicated the disassembly of hydrogen bonding (FIG. 83,panel C). The sample became turbid again when it was cooled back to roomtemperature, which indicated the reformation of hydrogen bonding and thereversibility of the process (FIG. 83, panel D).

Conjugation Reaction and Particle Characterization

Three steps were involved in synthesizing and characterizing thenanoparticles conjugated with the thermosensitive polymers, as shown inFIG. 84. (1) PAAc and PAAm were conjugated to cystamine and3,3′-dithiodipropionic acid (DDA) respectively which contain disulfidebonds. (2) PAAc-cystamine or PAAm-DDA was attached to the surface ofgold particles through the disulfide bond. (3) The particles wereseparated from the unreacted molecules by using centrifugation andcharacterized by using dynamic light scattering (DLS) and UV-visspectroscopy.

PAAc was conjugated to cystamine using the zero-length cross-linkingreagent, EDAC (1-ethyl-3-[3-(dimethylamino)propyl]carbodiimide).Different pH conditions were used to test the conjugation efficiencybetween PAAc and cystamine. An excess amount of PAAc was used to ensurethe complete reaction of cystamine. The fluorescamine assay was utilizedto test the amount of the unreacted primary amines on cystamine, whichindicated the conjugation efficiency. The results are shown in Table 16.The reactions were efficient at neutral and slightly basic conditions.Conjugation efficiencies above 95% were consistently achieved for allthe samples. Similar reaction conditions were used for the reaction ofPAAm with DDA.

TABLE 16 Conjugation efficiency of PAAc-cystamine at various pHconditions pH Efficiency (24 h) Efficiency (48 h) MES_pH4 7.2 96.1%96.6% MES_pH6 8.0 97.7% 95.5% MES_pH8 9.1 96.5% 97.8%PAAc-Gold and PAAm-Gold Conjugation

Disulfide bonds on PAAc-cystamine and PAAm-DDA were used to replace thecitrate on the surface of the gold nanoparticles through ligandexchange. PAAc-cystamine or PAAm-DDA was mixed with citrate goldnanoparticles in DI water for 24 hours. Next, 10 μL of 5M NaCl was addedfor four consecutive days to increase the ionic strength of the solutionso that more ligands could access the gold surface. Centrifugation wasused to remove unreacted polymers and reagents in the suspensions.UV-visible spectroscopy and DLS were used to confirm the sizes ofPAAc-gold and PAAm-gold conjugations. The shift of the absorbance peakindicated the aggregation of the gold nanoparticles.

Various conditions were tested to generate stable PAAc-gold conjugation,as shown in Table 17. C—N linkage showed good stability in a broad pHrange from pH 4 to pH 9. The initial ligand replacement was tested withand without buffers.

TABLE 17 Stability of gold nanoparticles conjugated with PAAc Goldparticle PAAc- polyP- Sample size cystamine cystamine UV UV ID (nm) (0.1mM) (0.1 mM) Buffer (AS) (AP) Stability PAAc_10nm_polyP(13) 10 7.5 μL 22.5 μL MES 519.5 522 yes (0.5M) 120 μL PAAc_10nm_polyP(11) 10 15 μL  15μL MES 520 522 yes (0.5M) 120 μL PAAc_10nm_30_MES 10 30 μL — MES 527 —no (0.5M) 120 μL PAAc_10nm_30_BA 10 30 μL — BA 608 — no (0.25M) 30 μLPAAc_10nm_20_BA 10 20 μL — BA 617.5 — no (0.25M) 30 μL PAAc_10nm_30 1030 μL — — 535.5 — no PAAc_10nm_20 10 20 μL — — 533 — no PAAc_10nm_15 1015 μL — — 534.5 — no PAAc_15nm_15 15 15 μL — — 522 523 yes Abbreviationsused in the table: AS—after salt addition, and AP—after purification

Conjugation of PAAm-DDA with gold nanoparticles to form PAAm-gold wascharacterized and summarized in Table 18.

TABLE 18 Stability of gold nanoparticles conjugated with PAAm Goldparticle PAAm- polyP- Sample size DDA cystamine UV UV ID (nm) (0.1 mM)(0.1 mM) Buffer (AS) (AP) Stability PAAm_10nm_polyP(13) 10 7.5 μL  22.5μL MES 520.5 521 yes (0.5M) 120 μL PAAm_10nm_polyP(11) 10 15 μL  15 μLMES 518.5 521.5 yes (0.5M) 120 μL PAAm_10nm_30_MES 10 30 μL — MES 527526.5 no (0.5M) 120 μL PAAm_10nm_30_BA 10 30 μL — BA 521 524 yes (0.25M)3 μL PAAm_10nm_20_BA 10 20 μL — BA 519.5 521 yes (0.25M) 30 μLPAAm_15nm_15 15 15 μL — — 530 — no PAAm_15nm_15_BA 15 15 μL — BA 533 —no (0.25M) 30 μL PAAc_15nm_7.5_BA 15 7.5 μL  — BA 525.5 525.5 yes(0.25M) 30 μL Abbreviations used in the table: AS—after salt addition,and AP—after purificationReversible Particle Aggregation Upon Temperature Change

PAAc_10nm_polyP(13) and PAAm_10nm_polyP(13) were mixed at a 1:1 volumeratio. DLS and UV-visible absorbance were used to test the size of goldnanoparticles at different temperatures. The absorbance peaks ofPAAc_10nm_polyP(13) and PAAm_10nm_polyP(13) were 523.5 and 522,respectively. After mixing PAAc_10nm_polyP(13) and PAAm_10nm_polyP(13)at a 1:1 ratio at 20° C., the absorbance peak was 524 nm, which showedno significant increase. The aggregation of PAAc_10nm_polyP(13) andPAAm_10nm_polyP(13), if any, was caused by the formation ofintermolecular hydrogen bonding between PAAc and PAAm, which may notinduce any significant peak shift since the hard core of the particlesmay be still sufficiently separated.

DLS was also used to test the size distribution of gold nanoparticles atdifferent temperatures. The size of PAAc_10nm_polyP(13) andPAAm_10nm_polyP(13) peaked at 9 nm consistently at 25° C. and 37° C.

The size and size distribution of the mixture of PAAc_nm_polyP(13) andPAAm_nm_polyP(13) at 25° C., 33° C. and 37° C. are shown in FIG. 85.Aggregation was observed at 25° C. and 33° C. The size ofPAAcm_10nm_polyP(13) at 25° C. and 33° C. was 15.2 nm and 14 nmrespectively, while the original size of the gold nanoparticles by DLSwas about 9 nm. When the temperature was increased to 37° C., which wasabove the UCST of PAAc and PAAm, the hydrogen bonding disassembled andthe size of the gold nanoparticles reduced back to about 9 nm.

A mixture of PAAc_10nm_polyP(11) and PAAm_10nm_polyP(11) at a 1:1 ratioalso showed similar results of particle aggregation (FIG. 86). At 25°C., average size measured by DLS was 17.5 nm. When the temperature wasincreased to 37° C., a small peak at 8 nm appeared which indicated thedisassembly of the inter-molecular hydrogen bonding between PAAc andPAAm.

PAAc_10nm_polyP(11) or PAAm_10nm_polyP(11) had more PAAc or PAAm andless polyP on the surface of the gold nanoparticles as compared toPAAc_10nm_polyP(13) or PAAm_10nm_polyP(13). Thus, it was relatively moredifficult to disassemble all the hydrogen bonding and resuspend thenanoparticles back to their original size.

In order to generate bigger aggregation, PAAc or PAAm was conjugated tothe surface of gold nanoparticles alone without polyP. However, whenmixing PAAc_15 nm_15 and PAAm_10nm_20_BA at a 1:1 ratio, aggregation wasnot found.

Silica Nanoparticle (SNP) Synthesis

Experiments were performed with silica nanoparticles (SNPs) andpolyP-functionalized silica nanoparticles (SNP-P70) to measure theeffect of the silica particles' size and concentration on coagulation.Particles above 10 nm were synthesized following a modified Stobermethod and recovered using centrifugation. The different nanoparticlesizes were obtained by varying the amounts of tetraethoxysilane (TEOS)and ammonia (NH₄OH) (FIG. 87). Ludox silica nanoparticles below 10 nm(Sigma Aldrich) were also tested. Silica nanoparticles below 50 nm wereisolated by ultrafiltration and ultracentrifugation for coagulation andfunctionalization experiments. Yield of greater than 40% was achievedusing greater than 4% NH₄OH. Syntheses below 4% NH₄OH produced a yieldbelow 40% (FIG. 88). The lack of ammonia may have reduced catalysis ofthe TEOS hydrolysis reaction. Zeta potential tests showed that SNPs hada negative charge in simulated body fluid, which facilitated activationof the intrinsic pathway by activating FXII. Zeta potential did not showa significant systematic change in coagulation with respect to size orpH.

Clotting experiments described above compared the silica particles ateither a fixed concentration of 0.68 mg/mL (25 mg/mL stock solution) orat a fixed size of 55 nm to determine high activity range boundaries.Each particle formed an initial clot (R) between 3 and 5 min. Thethreshold for minimum R value occurred at a particle size of ˜30 nm.Experiments in which particles below 20 nm were synthesized exhibited abimodal size distribution when measured using DLS. The bimodal sizedistribution may be a result of a lack of ammonia.

Utilizing phospholipids which increase coagulation through FXa, R wasminimized to less than two minutes. In FIG. 89, the concentrationdependence of R for two SNP and SNP-P70 was examined. P70 was a polyPchain that was approximately 70mer in length, which was roughly the samesize as polyP produced by activated platelets as part of the coagulationcascade. At low particle concentrations, the R value was high (clottingtime was long). As the particle concentration increased, R decreaseduntil the threshold condition was met. For bare silica, the thresholdconcentration occurred at 0.54 mg/ml. SNP-P70 reached a threshold at aconcentration of 0.27 mg/ml, half that of bare SNP. Above the thresholdconcentration the R value remained low, until at much higherconcentration the particles may inhibit clotting due to particleaggregation or dilution of plasma factors over the particle's surfacearea.

Other parameters may also be evaluated, such as rate of clot formation,and clot size, since the agents attached to the particle may affect theinitial clot formation time, but could accelerate the clotting wheninitiated or result in the formation of a bigger clot. Tests confirmedthat the particles maintained stability and size, at all concentrations,indicating particle sizes varied due to synthesis conditions.

In addition to solid non-porous nanoparticles, large-pore mesoporousnanospheres (MSN) may be used to deliver procoagulant proteins such asthrombin, prothombin or tissue factor to wounds. The large pore size andincreased accessible surface may increase coagulation by allowingproteins to adsorb to the surface and activate. For example, orderedmesoporous nanoparticles in the 50-200 nm range size with a pore sizebetween 10-30 nm may be used.

Functionalizing the nanoparticles with polyP or prothrombin may enhancethe procoagulant nature of the particles. The polyP used was a ˜70-merlength (P70) that was similar in size to polyP secreted by humanplatelets during clotting. P70 directly adsorbed to silica was found toincrease the particle size by several nm. SNPs were tested with andwithout adsorbed polyP and found that P70-bound SNPs significantlydecreased clotting time when compared to bare SNP (FIG. 89). SNP-P70also improved clotting time when compared to P70 added directly toplasma. The SNP scaffold thus served as a mechanism to deliver the P70triggering agent to the wound to initiate clotting.

Experiments were performed using longer polyPs chains, such as ˜700-merpolyP (P700). PolyP with a size range above 500mers was shown toaccelerate the contact or intrinsic pathway by activating FXII. The P700was attached to the scaffolds using the same methods described above.Four different ratios of P700:SNP were tested—0.2, 0.4, 0.6, and 1.Similar to P70, clotting assays suggested that clot time decreased witha ratio of P700:SNP above 0.5. A 1:1 ratio minimized clot time (FIG.90).

Samples of SNP, SNP-P70, and SNP-P700 nanoparticles were used for polyPquantification and further coagulation tests. These tests revealed thatSNP-P70 particles with a concentration of roughly 25 nmol PO₄/mg SNP(quantified by hydrolysis) exhibited higher procoagulant activity thanSNP-P70 particles with a higher nmol Pat/mg SNP concentration.

In addition to TEG, the coagulation threshold response was also testedusing a thrombinspecific blue coumarin dye. A small concentration of dyewas added to the recalcified plasma. As clotting progressed and thrombinwas produced, the thrombin cleaved the coumarin dye causing the solutionto fluoresce. Rapid fluorescence signified the thrombin burst, which ledto clot formation. A fluorescence microscope captured the qualitativechange as shown in FIG. 70.

Thrombin generation was also monitored using a plate reader. By readingfluorescence every 10 seconds, the thrombin burst was identified. Asclotting occurred near the rapid rise section of the thrombin burst, theclot time was determined from the fluorescence data plot.

After determining the procoagulant activity of SNP-P70 under normalconditions as discussed above, the SNP-P70 TSPs were applied undertraumatic conditions. A traumatic injury can quickly develop intocoagulopathy, the fundamental breakdown of the human coagulationcascade. Though coagulopathy can exist either as a hypercoagulant orhypocoagulant form, as used herein coagulopathy is the fundamentalbreakdown of the coagulation cascade that impairs clot formation. In thepresence of trauma, the coagulopathic body becomes weakened such thatanticoagulant pathways take over and a clot cannot form.

Coagulopathy exists in three states known as the “lethaltriad”—dilution, hypothermia, and acidosis. Each damages the cascade ina specific way. In a coagulopathic state, all three states combine toinhibit clot formation. In these experiments, dilution was mimickedusing a phosphate buffered solution (PBS). Incubating plasma below theusual 37° C. was used to create hypothermic conditions. A dilutephosphoric acid solution was used to acidify the plasma below a pH of7.1 to create an acidosis condition. The experiments utilized a setconcentration of lipidated tissue factor (LTF)—0.5 ng/ml for TEG tests,0.185 ng/ml for fluorescence dye tests—to produce timely initiation ofthe coagulation cascade through the extrinsic pathway and the body'smain response to vessel injury. The SNP-P70 TSP was tested at 0.25 mg/mlwithout LTF to compare its ability to form clots.

Due to the loss of both procoagulant and anticoagulant factors fromblood loss, dilution begins to significantly inhibit clotting at the˜50% level. Using TEG and dye fluorescence, a dilution baseline wasestablished. SNP-P70 (at the threshold concentration of ˜0.25 mg/mlidentified in our TEG experiments) was used to reverse the coagulopathicconditions. SNP-P70 successfully hastened thrombin burst and clotformation. (FIGS. 91 and 92). FIG. 93 shows a graph of thrombingeneration times from 100% plasma to 25% plasma; i.e.: 100% is 100%plasma and 0% dilutant. FIG. 94 shows a graph of fluorescence over time,which indicated that adding SNP-P70 generated thrombin quickly evenunder severe plasma dilution.

Hypothermia, the second member of the lethal triad, occurs when the bodytemperature drops below 37° C. The drop in temperature leads to adecreased rate in the kinetics of many of the coagulation factors,especially formation of the tissue factor-FVIIa (TF-FVIIa) complexduring the initiation phase of coagulation. Unlike dilution wherefibrinogen deficit triggers the drop in clotting, hypothermia slowscoagulation but does not prevent it. The addition of SNP-P70 tohypothermic plasma resulted in improved coagulation across all TEGparameters. A coagulation index formula was used to show theprocoagulant nature of the SNP-P70 TSP at sub-normal body temperature.Coagulation index (CI) combines all four TEG facets—R, K, alpha, andMA—into a single value; the more positive the CI, the stronger theprocoagulant. FIG. 95 shows a graph of clot time vs. temperature, whichindicated that SNP-P70 TSPs initiated clots quicker under hypothermia.FIG. 96 shows a graph of Coagulation index (CI) vs. temperature, whichindicated that SNP-P70 improved clot formation compared to lipidatedtissue factor (LTF).

The above experiments showed that SNP-P70 lowered clot times whileforming strong clots as compared to bare SNP and LTF. Studies on FXIIdeficient plasma showed that SNP-P70 initiated clotting through FXacoagulation pathway. Finally, SNP-P70 was shown to decrease clot timeand quicken thrombin generation under coagulopathic conditions oftenfound in patients who have suffered a traumatic wound (e.g., dilutionand hypothermia).

While the present invention has been described with reference to thespecific embodiments thereof, it should be understood by those skilledin the art that various changes may be made and equivalents may besubstituted without departing from the true spirit and scope of theinvention. In addition, many modifications may be made to adapt aparticular situation, material, composition of matter, process, processstep or steps, to the objective, spirit and scope of the presentinvention. All such modifications are intended to be within the scope ofthe claims appended hereto.

What is claimed is:
 1. A hemostatic composition comprising ahemostatically effective amount of a hemostatic agent comprising: amaterial selected from the group consisting of iron oxide, diatomaceousearth, an aluminosilicate, an oxide of a transition metal, and titaniumdioxide, wherein the material is a nanoparticle; and a polyphosphatepolymer covalently attached to the nanoparticle.
 2. The hemostaticcomposition of claim 1, wherein the polyphosphate polymer is attached tothe nanoparticle through a linkage selected from the group consisting ofan ester linkage and a carboxylic acid linkage.
 3. The hemostaticcomposition of claim 1, wherein the nanoparticle comprises a surfacefunctionalized with (3-aminopropyl)triethoxysilane (APTES).
 4. Thehemostatic composition of claim 3, wherein the polyphosphate polymer isattached to the nanoparticle through a phosphoramidate linkage.
 5. Thehemostatic composition of claim 1, wherein the hemostatic agent furthercomprises a protecting agent attached to the hemostatic agent by anenzymatically-cleavable linking group.
 6. The hemostatic composition ofclaim 5, wherein the enzymatically-cleavable linking group is cleavableby an enzyme selected from the group consisting of thrombin (FactorIIa), Factor VIIa, Factor IXa, Factor Xa, Factor XIa, Factor XIIa,tissue plasminogen activator (tPA), urokinase plasminogen activator(uPA), activated protein C, and plasmin.
 7. The hemostatic compositionof claim 5, wherein the protecting agent comprises a polyethylene glycolpolymer.
 8. The hemostatic composition of claim 7, wherein thepolyethylene glycol polymer has a molecular mass of 1000 Da to 10,000Da.
 9. The hemostatic composition of claim 7, wherein the polyethyleneglycol polymer has a molecular mass of 1000 Da to 20,000 Da.
 10. Thehemostatic composition of claim 1, wherein the hemostatic agent furthercomprises a specific binding agent.
 11. The hemostatic composition ofclaim 10, wherein the specific binding agent specifically binds to aprotein or a peptide.
 12. The hemostatic composition of claim 11,wherein the specific binding agent comprises a protein binding aptameror peptide.
 13. The hemostatic composition of claim 11, wherein thespecific binding agent comprises a fibrin binding ligand.
 14. Thehemostatic composition of claim 13, wherein the specific binding agentcomprises CREKA (SEQ ID NO: 1).
 15. The hemostatic composition of claim1, further comprising a biologically active agent bound to thehemostatic agent.
 16. The hemostatic composition of claim 15, whereinthe biologically active agent is selected from the group consisting ofan enzyme, a phospholipid, a clotting cascade cofactor, an antibiotic,and an anti-inflammatory agent.
 17. The hemostatic composition of claim1, wherein the polyphosphate polymer comprises 20 to 1500 phosphatemonomers.
 18. The hemostatic composition of claim 1, wherein thehemostatic agent has a polyphosphate polymer to nanoparticle mass ratioof 1:1 to 1:5.
 19. The hemostatic composition of claim 1, wherein thenanoparticle has an average diameter of 750 nm or less.
 20. Thehemostatic composition of claim 1, wherein the nanoparticle has anaverage diameter of 250 nm or less.
 21. The hemostatic composition ofclaim 1, wherein the hemostatic composition is a spray, aerosol, gel, orcement.
 22. A medical device comprising: a hemostatic composition ofclaim 1; and a sterile substrate on which the hemostatic composition isdisposed.
 23. The device of claim 22, wherein the substrate is adaptedfor delivery of the hemostatic composition to a bleeding wound.
 24. Thedevice of claim 23, wherein the substrate is a sponge, gauze, bandage,swab, pillow or sleeve.
 25. The device of claim 23, further comprising asealed package containing the hemostatic composition.
 26. A method ofpromoting blood clotting at a hemorrhage site, comprising: administeringto a hemorrhage site in a subject the hemostatic composition of claim 1for a period of time sufficient to at least initiate blood clotting atthe hemorrhage site.
 27. The method of claim 26, wherein the hemorrhagesite is an external hemorrhage site and the administering comprisesapplying the hemostatic composition to the external hemorrhage site. 28.The method of claim 26, wherein the hemorrhage site is an internalhemorrhage site, and the hemostatic agent further comprises a protectingagent attached to the hemostatic agent by an enzymatically-cleavablelinking group, and the administering comprises intravenouslyadministering the hemostatic composition to the subject.
 29. Thehemostatic composition of claim 1, wherein the nanoparticle is solid.